Drug delivery devices and methods for drug delivery

ABSTRACT

Drug delivery devices and methods of administering drugs to patients are provided. A device includes a reservoir containing a drug. The reservoir is defined by a wall having a water-permeable portion, such that the water-permeable portion permits water to enter the device and contact the drug. A restraining plug closes off an opening of the device such that transient microchannels form between an elastic portion of the device and the restraining plug, upon the generation of a sufficient pressure within the reservoir, to release the drug from the device. Methods of treating patients for neurogenic detrusor overactivity resulting from a spinal cord injury and/or for idiopathic overactive bladder and urinary incontinence are also provided.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.16/302,061, filed Nov. 15, 2018, which is a U.S. national stageapplication of International Application No. PCT/US2018/016463, filedFeb. 1, 2018, which claims priority benefit of U.S. ProvisionalApplications No. 62/453,333, filed Feb. 1, 2017, and 62/480,744, filedApr. 3, 2017, the disclosures of which are incorporated herein byreference.

BACKGROUND

This disclosure generally relates to medical devices deployable in vivofor controlled drug delivery, and more particularly relates to suchdevices having a water-permeable wall portion and one or more mechanismsfor providing controlled drug release from the device.

Many current drug delivery devices rely on one or more orifices in thesidewall or end of the device, to permit the release of a drugtherefrom. However, such orifices, especially those disposed in asidewall of a device, may be susceptible to encrustation and cloggingafter the drug delivery device is deployed in a patient. A cloggedorifice is undesirable because it often leads to less reproducible drugrelease, or it may prevent drug release entirely. Additionally, orificesdisposed in ends of the device provide release only at the terminalportion of the device, which may not be desirable for all deviceconfigurations and drug formulations.

In other cases, a drug delivery device may not have a release orificeand release of drug is controlled by diffusion from a matrix materialand/or through a wall bounding a reservoir of the drug. Suchconfigurations, which rely on diffusion, however, may limit the drugrelease kinetics that can be achieved and/or may limit the range ofsuitable materials of construction to ones that lack the desiredbiocompatibility, stability, sterilizability, and mechanical properties,including manufacturability, wall thickness, flexibility, etc.

Accordingly, a need exists for drug delivery devices that overcome oneor more of these disadvantages. A need also exists to provide improvedmethods and drug delivery systems for treating patients with idiopathicoveractive bladder and urinary incontinence and patients with neurogenicdetrusor overactivity resulting from spinal cord injury.

SUMMARY

In one aspect, a drug delivery device is provided, including a body thathas a wall bounding a reservoir defined within the body, the wall havingat least one preformed through-hole disposed therein and having awater-permeable portion, the body including an elastic portion; a drugformulation which includes a drug, the drug formulation being disposedwithin the reservoir; and at least one restraining plug closing off anopening of the body and contacting the elastic portion of the body, theopening being in fluid communication with the reservoir, wherein thewater-permeable portion of the wall is configured to permit water toenter the drug delivery device and contact the drug formulation locatedin the reservoir, wherein release of the drug from the device iscontrolled by (i) release of the drug through the at least one preformedthrough-hole in the wall, and (ii) release of the drug through thetransient formation of one or more microchannels between the elasticportion of the body and the at least one restraining plug, extending tothe opening, upon the generation within the reservoir of a hydrostaticpressure effective to form the one or more microchannels.

In another aspect, a drug delivery device is provided, including atubular body that has a wall bounding a reservoir defined within thebody, the wall having a water-permeable portion and an elastic portionhaving at least one preformed release port disposed therein; a drugformulation which includes a drug, the drug formulation being disposedwithin the reservoir, wherein the water-permeable portion of the wallpermits water to enter the drug delivery device and contact the drugformulation located in the reservoir; and at least one restraining plugsecured within the reservoir in contact with the elastic portion of thebody and adjacent the at least one preformed release port, such that theat least one restraining plug controls release of the drug from thedevice, via the at least one preformed release port, by the transientformation of one or more microchannels between the elastic portion ofthe body and the at least one restraining plug, extending to the atleast one preformed release port, upon the generation of a hydrostaticpressure within the reservoir effective to form the one or moremicrochannels.

In yet another aspect, methods of administering a drug to a patientusing one of the above-described devices are provided, includinginserting the drug delivery device into a lumen or body cavity of apatient; and permitting water influx into the reservoir to develop apressure in the reservoir effective to cause the drug to flow from thereservoir and out of the device and into the lumen or body cavity.

In still yet another aspect, a method of treating a patient in need oftreatment for neurogenic detrusor overactivity (NDO) resulting from aspinal cord injury (SCI) is provided, including locally administering aneffective amount of trospium into the urinary bladder of the patientcontinuously over a treatment period of 30 to 60 days.

In still yet another aspect, a method of treating a patient in need oftreatment for idiopathic overactive bladder (iOAB) and urinaryincontinence is provided, including locally administering an effectiveamount of trospium into the urinary bladder of the patient continuouslyover a treatment period of 30 to 60 days.

BRIEF DESCRIPTION OF THE DRAWINGS

Referring now to the drawings, which are meant to be exemplary and notlimiting, and wherein like elements are numbered alike. The detaileddescription is set forth with reference to the accompanying drawingsillustrating examples of the disclosure, in which use of the samereference numerals indicates similar or identical items. Certainembodiments of the present disclosure may include elements, components,and/or configurations other than those illustrated in the drawings, andsome of the elements, components, and/or configurations illustrated inthe drawings may not be present in certain embodiments.

FIG. 1A is a cross-sectional side view of one embodiment of an elasticportion of a device containing a restraining end plug.

FIG. 1B is a cross-sectional end view of the embodiment of FIG. 1A.

FIG. 1C is a cross-sectional side view of the device of FIG. 1A when thereservoir is not under an osmotic pressure.

FIG. 1D is a cross-sectional side view of the device of FIG. 1A when thereservoir is under an osmotic pressure.

FIG. 2 is a cross-sectional side view of one embodiment of a devicehaving a preformed sidewall orifice and two restraining end plugs.

FIG. 3A is a plan view of one embodiment of a device having a preformedsidewall orifice and two restraining end plugs.

FIG. 3B is a cross-sectional magnified view of one of the end plugs ofFIG. 3A.

FIG. 3C is an exploded perspective view of the end plug of FIG. 3B.

FIG. 4 is a cross-sectional end view of one embodiment of a drugdelivery device.

FIG. 5 illustrates various embodiments of restraining plugs inaccordance with the present disclosure.

FIG. 6 is a cross-sectional view illustrating the restraining plugs ofFIG. 5 in use as the end plugs of a drug delivery device.

FIG. 7 illustrates deployment of a drug delivery device from adeployment instrument.

FIG. 8 illustrates deployment of a drug delivery device in a patient.

FIG. 9A is a plan view of one embodiment of a drug delivery devicehaving restraining plugs and a preformed release port.

FIG. 9B is an enlarged cross-sectional view of the device of FIG. 9A.

FIG. 10A is a plan view of one embodiment of a drug delivery devicehaving restraining plugs and a preformed release port.

FIG. 10B is an enlarged cross-sectional view of the device of FIG. 10A.

FIG. 11 is a graph showing drug release rate over time for a drugdelivery device tested in the Examples.

FIG. 12 is a graph showing drug release rate over time for a drugdelivery device tested in the Examples.

FIG. 13 is a graph showing drug release rate over time for a drugdelivery device tested in the Examples.

FIG. 14 is a graph showing drug release rate over time for various drugdelivery devices tested in the Examples.

FIG. 15 is a graph showing cumulative drug release over time for variousdrug delivery devices tested in the Examples.

FIG. 16 is a graph showing drug release rate over time for various drugdelivery devices tested in the Examples.

FIG. 17 is a graph showing cumulative drug release over time for variousdrug delivery devices tested in the Examples.

FIG. 18 is a graph showing drug release rate over time for various drugdelivery devices tested in the Examples.

FIG. 19 is a graph showing drug release rate over time for various drugdelivery devices tested in the Examples.

FIG. 20 is a graph showing drug release rate over time for various drugdelivery devices tested in the Examples.

FIG. 21 is a graph showing drug release rate over time for various drugdelivery devices tested in the Examples.

FIG. 22 is a graph showing cumulative drug release over time for variousdrug delivery devices tested in the Examples.

FIG. 23 is a graph showing percent drug release over time for variousdrug delivery devices tested in the Examples.

FIG. 24 is a graph showing drug release rate over time for various drugdelivery devices tested in the Examples.

DETAILED DESCRIPTION

Drug delivery devices 50 having a water-permeable wall portion 64bounding a reservoir 60 (also referred to herein as a “reservoir lumen”or a “drug reservoir lumen”) containing a payload 58, such as a drugformulation, are provided herein, along with methods for delivering thepayload 58 from the device 50. As shown in FIG. 2, the water-permeablewall portion 64 may generally be configured to permit water to enter thedevice and contact the drug formulation (i.e., payload) 58 located inthe reservoir 60, to facilitate release of the drug 58 from the device.For example, osmotically driven water influx into the reservoir 60 maygenerate a pressure within the reservoir 60 that drives release of thedrug 58 from the reservoir 60 via one or more mechanisms. For example,in embodiments described herein, release of the drug 58 from the devicemay occur through one or more preformed sidewall orifices 66 (see FIG.2) and/or through the transient formation of one or more microchannels62 leading to a preformed release port 68 or other opening (see FIG. 9).In certain embodiments described herein, combinations of these releasemechanisms are employed to provide the desired drug release profile andto overcome the disadvantages discovered in devices exclusively relyingon one or more preformed orifices for drug release.

In particular, it has been discovered that implantable intravesical drugdelivery devices in which preformed orifices in the side or end walls ofthe device are utilized for the release of drug from the device aresusceptible to encrustation and clogging of the orifices followingintravesical deployment, or implantation. Thus, in certain embodiments,as shown in FIG. 2, drug delivery devices 50 of the present disclosurecontain one or more predefined orifices 66 in the sidewall or end of thedevice in combination with a one-way valve structure involving thetransient formation of one or more microchannels 62 leading to apreformed release port or other opening, upon the generation of ahydrostatic pressure effective to form the one or more microchannels inthe reservoir 60. For example, the generation of a hydrostatic pressurein the reservoir 60 that exceeds the threshold pressure for thetransient formation of microchannels 62 may occur when the preformedorifice(s) 66 is partially or fully clogged or when release through theorifice(s) 66 does not occur quickly enough to relieve the hydrostaticpressure within the reservoir 60. In some embodiments, as shown in FIGS.9 and 10, a preformed release port 68 in the sidewall or end of thedevice is provided in combination with a restraining plug 56 that blocksaccess to the release port 68, absent the generation of a hydrostaticpressure in the reservoir effective to form the one or moremicrochannels 62 extending to the release port 68.

It has been discovered that controlled release of drug can be achievedwith devices having improved one-way valve release mechanisms, alone orin combination with other release mechanisms. For example, controlledrelease of drug can be achieved with the transient formation ofmicrochannels through which a fluidized drug can be dispensed from adelivery device. The microchannels form at an interface of devicecomponents in response to a hydrostatic pressure developed in a drugreservoir. Drug delivery devices configured to induce and utilize suchmicrochannels (i.e., which are distinct from preformed orifices) havebeen developed, which avoid or alleviate the potential problemsassociated with conventional drug release mechanisms, includingprecision miniature orifices that may increase component cost and therisk of clogging, or that are limited by diffusion through or fromanother material.

In embodiments, the drug delivery device 50 includes a device body 52having at least one water-permeable wall portion 64 bounding a drugreservoir 60 defined within the body 52. A drug formulation 58 whichcomprises a drug is loaded into the defined drug reservoir 60. The body52 includes an elastic portion 54 in fluid communication with the drugreservoir 60. The device 50 further includes a restraining plug 56 thatcontacts the elastic portion 54 of the body 52 and controls release ofthe drug 58 from the device 50 by the transient formation of one or moremicrochannels 62 between the elastic portion 54 of the body 52 and theat least one restraining plug 56.

The term “microchannels,” as used herein, refers to a passageway orsystem of passageways through which drugs can exit the devices describedherein. In embodiments, the microchannels form in response tohydrostatic pressure that accumulates in the water-permeable body due toosmotically driven water influx; when the hydrostatic pressure increasesabove a certain threshold, the microchannels form, thereby forcing atleast a portion of drug out of the device and relieving the hydrostaticpressure accumulation in the drug reservoir. The microchannel maycollapse at least partially as the hydrostatic pressure has beenrelieved. This process repeats itself until all or a substantial portionof the drug has been released, or the osmotically driven water influx isinsufficient to continue the process.

The microchannels may form anywhere along the inner surface of theelastic portion of the water-permeable body, thereby significantly andbeneficially reducing the likelihood of complete clogging—even wheninsoluble excipients are used in the drug formulation. Advantageously,the microchannels, unlike an orifice, may reduce or eliminate thepotential risk of sudden drug discharge when the device is compressed ordeformed. For example, when the drug delivery devices are surrounded bybody fluid and disposed in an environment that exposes the devices tomoderate external mechanical stress (such as during urination when thedevice is a deployed intravesical drug delivery device), drugs are lesslikely to be discharged through the microchannels.

FIGS. 1A-1D show one embodiment of the microchannels in a drug deliverydevice. Device 50 includes a body, or housing, 52 having an elasticportion 54 with a restraining plug 56 inserted into an opening in thebody 52 such that the elastic portion 54 is positioned against (around)an outer surface of the restraining plug 56. As indicated by the dashedline arrows, water diffuses through a water-permeable wall 64 of thebody 52 and enters the drug reservoir 60, forming fluidized drug 58,which for example may be an aqueous solution comprising the drug 58initially loaded in the reservoir 60. Hydrostatic pressure in thereservoir 60 causes the fluidized drug 58 to be pushed out of thereservoir 60 between the elastic portion 54 and the restraining plug 56,through microchannels 62 that are formed therebetween, for example byelastic deformation of one or both of the interfacing surfaces. FIG. 1Cillustrates the device in a state in which hydrostatic pressure in thereservoir has not reached the threshold such that any microchannels areformed between the elastic portion 54 and the restraining plug 56. Inthe embodiment illustrated in FIGS. 1A 1B, and 1D, the microchannel 62is shown as forming between the reservoir 60 and the terminal(preformed) opening 72 of the device 50; however, as described below, insome embodiments, the device 50 is configured such that the microchannel62 forms between the reservoir 60 and a release port 68 defined in thesidewall or a closed end of the device.

The devices, systems, and methods disclosed herein, build upon somefeatures and aspects of the devices, systems and methods described inthe following Patent Application Publications: U.S. 2016/0199544 (Lee etal.); U.S. 2012/0089122 (Lee et al.); U.S. 2012/0089121 (Lee et al.);U.S. 2011/0152839 (Cima et al.); U.S. 2010/0331770 (Lee et al.); U.S.2010/0330149 (Daniel et al.); U.S. 2009/0149833 (Cima et al.); and U.S.2007/0202151 (Lee et al.), which, in pertinent part, are incorporated byreference herein.

The Drug Delivery Device

An embodiment of a drug delivery device is illustrated in FIGS. 3 and 4.The device includes a water-permeable body 52 having a drug reservoirportion 78 and a retention frame portion 76. As used herein, the term“drug reservoir portion” refers to the portion of the device that formsand defines the “drug reservoir” or “drug reservoir lumen”. As such,these terms are used with reference to the same or similar andoverlapping features of the devices. In FIG. 3A, the device 50 is shownin a relatively expanded shape suited for retention in the body, e.g.,in the urinary bladder. As shown in FIG. 7, the device 700 may also bedisposed in a relatively lower-profile shape for deployment through thechannel of a deployment instrument 702, such as a cystoscope or othercatheter. Following deployment into the body, the device may assume therelatively expanded shape to retain the drug delivery device in thebladder, or other body cavity or lumen.

In some embodiments, the intravesical device comprises a deploymentshape and a retention shape. For example, as shown in FIG. 7, the device700 may be elastically deformable between a relatively straightened oruncoiled shape suited for insertion through a lumen into the bladder ofthe patient (the deployment shape) and a retention shape suited toretain the device within the bladder. For the purposes of thisdisclosure, the term “retention shape” generally denotes any shapesuited for retaining the device in the bladder, including but notlimited to a coiled or “pretzel” shape. A pretzel shape is shown in FIG.3A. The retention shape enables the device to resist becoming entrainedin urine and excreted when the patient voids. The terms “relativelyexpanded shape”, “relatively higher-profile shape” may be usedinterchangeably with “retention shape.” Similarly, the term “relativelylower-profile shape” may be used interchangeably with “deployment shape”and generally denote any shape suited for deploying the drug deliverydevice into the body, including the linear or elongated shape shown inFIG. 7 that is suited for deploying the device through the workingchannel of a catheter, cystoscope, or other deployment instrumentpositioned in a lumen of the body, such as the urethra. In embodiments,the drug delivery device may naturally assume the relatively expandedshape and may be elastically deformed, either manually or with the aidof an external apparatus, into the relatively lower-profile shape forinsertion into the body. Once deployed the device may spontaneously ornaturally (e.g., elastically) return to the initial, relatively expandedshape for retention in the body. In some embodiments, the device behaveslike a spring, deforming in response to a compressive load (e.g.,deforming the device into a deployment shape) but spontaneouslyreturning to a retention shape once the load is removed. In someembodiments, this shape changing functionality of the intravesicaldevice is provided by including a shape retention frame (i.e., a“retention frame”) in the device, as described hereinbelow.

In the illustrated embodiment of FIG. 4, the drug reservoir andretention frame portions 78, 76 of the drug delivery device arelongitudinally aligned and are coupled to each other (or integrallyformed together) along their length, although other configurations arepossible. For example, the drug reservoir portion 78 may be attached tothe retention frame portion 76 at discrete points but otherwise may beseparate or spaced apart from the retention frame portion 76.

As shown in FIG. 4, the drug delivery device includes an elastic orflexible device body 52 that defines a drug reservoir lumen 60 and aretention frame lumen 80. The drug reservoir lumen 60 is designed tohouse a drug formulation, such as a number of solid drug tablets 158, toform the drug reservoir portion 78. The retention frame lumen 80 isdesigned to house a retention frame 74 to form the retention frameportion 76. The illustrated lumens 78, 76 are discrete from each other,although other configurations are possible.

As shown in the cross-sectional view of FIG. 4, the device body 52includes a tube or wall 82 that defines the drug reservoir lumen 60 anda tube or wall 84 that defines the retention frame lumen 80. The tubes82, 84 and lumens 60, 80 can be substantially cylindrical, with the drugreservoir lumen 60 having a relatively larger diameter than theretention frame lumen 80, although other configurations can be selectedbased on, for example, the amount of drug to be delivered, the diameterof the retention frame, and deployment considerations such as the innerdiameter of the deployment instrument. The device body 52 may be formedintegrally, such as via molding or extrusion, although separateconstruction and assembly of the tubes 82, 84 is possible. The wall 84that defines the retention frame lumen 80 may extend along the entirelength of the wall 82 that defines the drug reservoir lumen 60, so thatthe retention frame lumen 80 has the same length as the drug reservoirlumen 60 as shown, although one wall may be shorter than the other wallin other embodiments. Further, the two walls 82, 84 are attached alongthe entire length of the device in the illustrated embodiment, althoughintermittent attachment can be employed. In one example, the wall 82 ofthe drug reservoir lumen 60 has an inner diameter of about 1.5 mm and anouter diameter of about 1.9 mm, while the wall 84 of the retention framelumen 80 has an inner diameter of about 0.5 mm and an outer diameter ofabout 0.9 mm. In another example, the wall 82 of the drug reservoirlumen 60 has an inner diameter of about 2.16 mm and an outer diameter ofabout 2.56 mm. However, the inner and outer diameters of the wall 82 ofthe drug reservoir lumen 60 and the wall 84 of the retention frame lumen80 may be any suitable diameter. The cross-sectional area of the entirebody of the device 52 may be about 0.035 cm² or less. However, thecross-sectional area of the entire body of the device 52 may be anysuitable dimension.

As shown in FIG. 3A, the drug reservoir lumen may be loaded with anumber of drug units 158 in a serial arrangement. The drug units may betablets, such as mini-tablets. For example, between about 10 and about100 drug units may be loaded, such as between about 30 and about 70 drugunits, or more particularly between about 50 and 60 drug units. However,essentially any number of drug units may be used, depending upon thesizes of the reservoir and the drug units. The drug reservoir lumenincludes openings, which may be relatively circular openings at oppositeends of the drug reservoir lumen. These openings provide ingress for thedrug units to be placed into the drug reservoir lumen during deviceloading and assembly.

Restraining plugs, as described herein, may be disposed in the reservoirthrough the terminal openings of the device. The restraining plug andelastic portion may be disposed at any suitable position along thelength of the drug delivery device. In certain embodiments, as describedherein, a restraining plug may be disposed at or near the terminal endof the device. In other embodiments, a restraining plug may be disposedat or near the central portion of the device. In one embodiment, one ofthe terminal device openings has a restraining plug, and the opposedopening is sealed with a plug or other material that does not permit theformation of microchannels.

In some instances, as shown in FIGS. 1C and 1D, each of the restrainingplugs 56 may, as described herein, have an outer diameter that is largerthan the inner diameter of the drug reservoir lumen 60. In someembodiments, as shown in FIGS. 9A and 10A, the restraining plugs 56 maybe secured within the drug reservoir lumen 60 at the terminal ends ofthe device 50, such that the terminal ends or openings of the device 50are sealed, such as by an adhesive 70 or other suitable securementmeans. In other embodiments, as shown in FIGS. 1C-1D, the restrainingplugs 56 may be secured within the drug reservoir lumen 60 by anadhesive 70, but without sealing the lumen. In still other embodiments,the restraining plugs may be secured within the drug reservoir lumen byan external clamp disposed about the drug reservoir lumen. Therestraining plugs may be secured within the drug reservoir lumen by anymeans disclosed herein or a combination thereof, as long as it permitsthe desired formation of microchannels.

In certain embodiments, each of the restraining plugs may include acavity for receiving an end portion of the retention frame. In somecases, a number of restraining plugs can be positioned in the openingsor elsewhere along the length of the device. The restraining plugs maybe silicone plugs, ethylene vinyl acetate plugs, or a combinationthereof. In embodiments where one of the restraining plugs is omitted,the opening without the restraining plug is closed with any othersuitable biocompatible material. In one example, the material is anadhesive substance that is placed in the drug reservoir lumen inworkable form and cures therein. In some embodiments, a restraining plugis inserted into an opening of the drug reservoir lumen, and the otheropening of the drug reservoir lumen is sealed with an adhesive. In otherembodiments, both ends of the drug reservoir lumen may be sealed and oneor more restraining plugs may be located within the device near thesealed ends or spaced away from the sealed ends.

As shown in FIG. 4, the retention frame lumen 80 is loaded with theretention frame 74, which may be an elastic wire. The retention frame 74may be configured to return spontaneously to a retention shape, such asthe illustrated example “pretzel” shape or another coiled shape, such asthose disclosed in the patent application publications identified aboveand incorporated herein by reference. In particular, the retention frame74 may retain the device in the body, such as in the bladder. Forexample, the retention frame 74 may have an elastic limit and modulusthat allows the device 50 to be introduced into the body in a relativelylower-profile shape, permits the device to return to the relativelyexpanded shape once inside the body, and impedes the device fromassuming the relatively lower-profile shape within the body in responseto expected forces, such as the hydrodynamic forces associated withcontraction of the detrusor muscle and urination. Thus, the device maybe retained in the body once deployed, limiting or prevent accidentalexpulsion.

The material used to form the device body 52, at least in part, may beelastic or flexible to permit moving the device between deployment andretention shapes. When the device is in the retention shape, theretention frame portion 76 may tend to lie on the interior side of thedrug reservoir portion 78, although the retention frame portion 76 canbe positioned inside, outside, above, or below the drug reservoirportion 78 in other cases. At least a portion of the material used toform the device body 52 also is water-permeable so that solubilizingfluid (e.g., urine or other bodily fluid) can enter the drug reservoir60 to solubilize the drug units 158 once the device is deployed. Forexample, silicone, ethylene vinyl acetate (EVA), thermoplasticpolyurethanes, or another biocompatible elastomeric material may be usedto form the device body.

In one embodiment in which the drug delivery device is designed to beinserted in the bladder, the drug delivery device is designed to beinserted into (and optionally retrieved from) the bladder through theurethra cystoscopically. Thus, the device may be sized and shaped to fitthrough a narrow tubular path of a deployment instrument, such as acatheter or cystoscope.

The exact configuration and shape of the drug delivery device may beselected depending upon a variety of factors including the specific siteof deployment, route of insertion, drug, dosage regimen, and therapeuticapplication of the device. The design of the device may minimize thepatient's pain and discomfort, while locally delivering atherapeutically effective dose of the drug to a tissue site (e.g.,urothelial tissue) in a patient.

The Device Body/Drug Reservoir Portion

As shown in FIGS. 1-3, 9, and 10, the drug delivery device 50 has a body52, e.g., a housing, that has a drug reservoir 60, which includes awater-permeable wall 64, and that includes an elastic portion 54 forengagement with the one or more restraining plugs 56. The drug reservoir60 is at least partially defined by the water-permeable wall 64. Thatis, the device includes a “water-permeable body,” which, as the phraseis sometimes used herein, includes any structure having at least aportion that is water-permeable. In embodiments, the water-permeablebody is made entirely from a water-permeable material. In otherembodiments, the water-permeable body is made from a water-permeablematerial and a non-water-permeable material. In further embodiments, thewater-permeable body is made from a material having at least onewater-permeable portion and at least one non-water-permeable portion. Asused herein, a wall or material is “water-permeable” when it permits afluid to enter the drug delivery device, e.g., by transwall diffusion,and contact the drug formulation located in a reservoir within thedevice body.

The body 52 of the drug delivery devices 50 described herein alsoincludes at least one elastic portion 54. The elastic portion 54 of thedevice body 52 may be the same as or distinct from the water-permeableportion 64 of the device body 52 described in the preceding paragraph.In certain embodiments, as shown in FIG. 1A, the restraining plugs 56contact the at least one elastic portion 54 of the device body 52 toclose off an opening the body, which the opening is in fluidcommunication with the drug reservoir 60 within the device, therebyenclosing the drug 58 within the drug reservoir 60.

In some embodiments, all of the elastic portions of the device body arecontacted with restraining plugs that permit drug release as describedherein. In other embodiments, one or more of the elastic portions of thedevice body are contacted with restraining plugs that permit drugrelease as described herein and the remaining elastic portions of thebody are sealed by other suitable means, such as a cap, an adhesive,heat-sealing, soldering, solvent welding, or a combination thereof.

Generally, the length of the elastic portion should equal or exceed thelength of the portion of the restraining plug that contacts the elasticportion of the device body, so that formation/use of the microchannelsis not precluded, for example by an inelastic portion of the devicebody.

In embodiments, the elastic portion 54 of the body 52 is formed from amaterial that permits the formation of microchannels 62, ormicropathways, between the inner surface of the elastic portion 54 andthe restraining plug 56 when hydrostatic pressure builds up in the drugreservoir 60. As described in detail herein, the micropathways mayextend along the surface of the restraining plug/elastic portion fromthe drug reservoir to either an unsealed distal opening of the devicebody, as shown in FIGS. 1-3, or a preformed release port adjacent therestraining plug, as shown in FIGS. 9-10. The elastic portion mayinclude materials that are water-permeable, water-impermeable, or acombination thereof.

In a first aspect, as shown in FIGS. 1A-1D, the drug delivery devices 50described herein include one or more restraining plugs 56 in contactwith the elastic portion(s) 54 of the device body 52, to permit drugrelease via the distal opening(s) of the device body, as described inU.S. Patent Application Publication 2016/0008271 to Lee, which isincorporated by reference herein in relevant part. However, in contrastto the no-orifice (i.e., no predefined aperture system) of U.S. PatentApplication Publication 2016/0008271 to Lee, in certain embodiments, asshown in FIGS. 2 and 3A, the devices include at least one preformedthrough-hole (i.e., orifice) 66 disposed in a wall of the device body52.

Thus, in certain embodiments, as shown in FIGS. 1-4, a drug deliverydevice 50 includes a body 52 that has a wall bounding a reservoir 60defined within the body 52, the wall having at least one preformedthrough-hole 66 disposed therein and including a water-permeable portion64, the body 52 including an elastic portion 54; a drug formulation 58which contains a drug, the drug formulation 58 being disposed within thereservoir 60; and at least one restraining plug 56 closing off anopening of the body 52 and contacting the elastic portion 54 of the body52, the opening being in fluid communication with the reservoir 60. Thewater-permeable portion 64 of the wall is configured to permit water toenter the drug delivery device 50 and contact the drug formulation 58located in the reservoir 60 and release of the drug 58 from the device50 is controlled by at least one of (i) release of the drug 58 throughthe at least one preformed through-hole 66 (i.e., aperture, orifice) inthe wall, and (ii) release of the drug through the transient formationof one or more microchannels 62 between the elastic portion 54 of thebody 52 and the at least one restraining plug 56, extending to theopening, upon the generation of a hydrostatic pressure effective to formthe one or more microchannels 62. In these embodiments, the restrainingplugs 56 may be partially or wholly unsealed at the distal end openingsof the device 50. Such systems have been found to provide consistent andreproducible drug release profiles, while providing a relief valvesystem that beneficially provides release of the drug when thethrough-hole is partially or fully clogged. Thus, the device may operateto release drug via the preformed orifice unless and until thehydrostatic pressure within the drug reservoir reaches a thresholdpressure of the restraining plug(s), at which point release via therestraining plugs occurs. For example, release of the drug through theat least one preformed through-hole may be osmotically driven.

Beneficially, this device design provides drug release at the sideand/or center of the device, which provides increased device designflexibility as well as potential manufacturability improvements ascompared to devices in which the release of the drug occurs only throughthe distal openings of the device.

In a second aspect, as shown in FIGS. 9-10, the drug delivery devices 50described herein include sealed distal ends (shown sealed with adhesive70), with one or more restraining plugs 56 in contact with the elasticportion(s) 54 of the device body 52, to permit drug release viapreformed release port(s) 68 in the device body 52 (e.g., sidewall)adjacent the restraining plug 56. The elastic portions 54 may be at ornear the ends of the device 50 (as shown in FIGS. 9-10), or may beotherwise disposed along the length of the device, such as at or nearthe center of the device. The retraining plug(s) 56 may be situatedadjacent the one or more preformed release port(s) 68 in the device body52, such that the restraining plug(s) 56 cover, and effectively close,the preformed release port(s) 68 when the threshold hydrostatic pressurewithin the drug reservoir 60 has not been reached. In such embodiments,the restraining plugs 56 and elastic portions 54 of the device may besimilar to those described above and in U.S. Patent ApplicationPublication 2016/0008271 to Lee, except that the one or moremicrochannels 62 transiently formed upon the drug reservoir 60 reachinga threshold hydrostatic pressure extend from the drug reservoir 60 tothe preformed release port(s) 68.

Thus, in certain embodiments, as shown in FIGS. 9-10, a drug deliverydevice 50 includes a tubular body 52 that comprises a wall bounding areservoir 60 defined within the body, the wall having a water-permeableportion 64 and an elastic portion 54 having at least one preformedrelease port 68 (e.g., through-hole, aperture, orifice, slit) disposedtherein; a drug formulation 58 which contains a drug, the drugformulation 58 being disposed within the reservoir 60, wherein thewater-permeable portion 64 of the wall permits water to enter the drugdelivery device and contact the drug formulation 58 located in thereservoir 60; and at least one restraining plug 56 secured within thereservoir 60 in contact with the elastic portion 54 of the body 52 andadjacent the at least one preformed release port 68, such that the atleast one restraining plug 56 controls release of the drug from thedevice, via the at least one preformed release port 68, by the transientformation of one or more microchannels 62 between the elastic portion 54of the body and the at least one restraining plug 56, extending to theat least one preformed release port 68, upon the generation of ahydrostatic pressure within the reservoir 60 effective to form the oneor more microchannels 62. In certain of these embodiments, the at leastone preformed release port 68 is a through-hole or a slit disposed inthe wall of the body 52.

Any suitable number and location of restraining plugs 56 and preformedrelease ports 68 may be used, to achieve the desired drug releaseprofile. For example, as shown in FIG. 9B, the device 50 may include twopreformed ports 68, here shown as apertures, spaced 180 degrees from oneanother in a tubular device body 52, such that a single restraining plug56 is positioned adjacent both apertures. As shown in FIG. 9B, a pair ofapertures 68 and a corresponding restraining plug 56 may be provided ator near each distal end of the device. For example, as shown in FIG.10B, a single preformed port 68, here shown as a slit, may be disposedadjacent each restraining plug 56. As shown in FIG. 10B, a preformedport 68 and a corresponding restraining plug 56 may be provided at ornear each distal end of the device.

In such embodiments, a suitable adhesive 70, or other sealing meansdescribed herein, may be used to seal the ends of the device body. Incertain embodiments, the restraining plug 56 is sealed in place via theadhesive 70 or other sealing means sealing the end(s) of the devicebody, or via another adhesive. Such device designs may reduce complexityand variability associated with manufacturing and assembly of thebeveled end plug used when release is from the at least partiallyunsealed end opening of the device. Further, such release ports allowfor the creation of check valves on the side and/or at the middle of thedevice, allowing drug release from any location along the device, whichdecreases the limitations of the design. Additionally, locating releaseof the drug away from the ends of the device beneficially allows for arounded (i.e., non-trimmed) device end, such as a sphere or ball-shapedend design, which reduces imperfections that may serve as nucleationpoints for encrustation, at the ends. Further, such device designsadvantageously allow for increasing the flexibility and bendability ofthe terminal ends of the device.

In certain embodiments, the device also includes at least one preformedthrough-hole disposed in the wall of the body, as described above, incombination with the preformed release port adjacent a restraining plug,such that release of the drug from the device is further controlled byrelease of the drug through the at least one preformed through-hole inthe wall.

In embodiments in which the drug formulation is solid or semi-solid, asdescribed in further detail below, the device may be configured topermit, in vivo, water to diffuse through the water-permeable portion ofthe wall and into the reservoir to solubilize the drug formulation.

The devices described herein have been discovered to advantageouslyprovide controlled release of drug via these improved one-way valverelease mechanisms, alone or in combination with other releasemechanisms such as preformed sidewall orifices, which may experienceclogging. Thus, the devices described herein provide for a longerduration of drug delivery as compared to devices with sidewall releaseorifices alone, which may be susceptible to encrustation.

Specifically, controlled release of drug can be achieved with thetransient formation of microchannels through which a fluidized drug canbe dispensed from a delivery device, either through the distal endopening of the device or through one or more preformed release portsadjacent a restraining plug. The microchannels form at an interface ofdevice components in response to a hydrostatic pressure developed in adrug reservoir, such that the device parameters can be tailored torelease drug only when a certain threshold hydrostatic pressure isreached within the drug reservoir.

To facilitate the formation of microchannels, the elastic portion 54 ofthe device body 52 and the restraining plugs 56 may be formed frommaterials having a certain elasticity or hardness. In embodiments, theShore durometer of the elastic portion of the body is lower than theShore durometer of the restraining plug. In one embodiment, the Shoredurometer of the elastic portion of the body is from about 40A to about60A, and the Shore durometer of the restraining plug is from about 70Ato about 100A. In another embodiment, the Shore durometer of the elasticportion of the body is from about 45A to about 55A, and the Shoredurometer of the restraining plug is from about 75A to about 85A. In afurther embodiment, the Shore durometer of the elastic portion of thebody is about 50A, and the Shore durometer of the restraining plug isabout 80A. In yet another embodiment, the Shore durometer of the elasticportion of the body is from about 40A to about 60A, and the Shoredurometer of the restraining plug is about 97A. In some embodiments, inwhich the restraining plug is at or near the end of the device and apreformed release port in the device body is adjacent the restrainingplug, the durometer of the restraining plug may be further reduced todecrease the rigidity of the end of the device.

In embodiments, the device body 52 may contain two or more elasticportions 54 having different elasticities that contact two or morerestraining plug 56 having different elasticities. This configurationcan be useful for controlling drug release from two or more differentreservoirs having drugs of different solubilities, desired releaserates, etc. For example, a water-permeable body may have a first and asecond elastic portion made from two different materials having Shoredurometers of 45A and 55A, respectively, and inserted into the first andthe second elastic portion may be a first and a second restraining plugmade from two different materials having Shore durometers of 75A and85A, respectively.

In one embodiment, the device body is made entirely from an elasticmaterial. In other embodiments, the body is made from at least oneelastic material and at least one inelastic material. In furtherembodiments, the body is made from a material having at least oneelastic portion and at least one inelastic portion.

The elastic portion 54 of the device body 52 may be any shape thatpermits the insertion of a restraining plug 56 and the creation ofinterference fit between the elastic portion 54 and the plug 56. Whenviewed in cross-section, the lumen of the elastic portion may benon-polygonal. For example, the cross-section may be round,substantially round, or oval-shaped. In some embodiments, the shape ofthe lumen of the elastic portion substantially conforms to the shape ofthe restraining plug.

The device body 52 generally may be made from any biocompatiblematerial, so long as at least a portion of the body 64 iswater-permeable. The elastic portion 54 of the body 52 that contacts therestraining plug 56 may be made from any biocompatible material thatpermits the formation of one or more microchannels 62 through which drugmay exit the device 50.

In one embodiment, the device body 52 includes an elongated tube. Aninterior of the tube may define one or more drug reservoirs 60, and adrug formulation 58 may be housed in the drug reservoir(s) 60. Forexample, the elongated tube may be annular in shape with the annulus,i.e., the lumen of the tube, serving as the drug reservoir. In otherembodiments, the drug reservoir portion is in a form other than a tube.The release rate of the drug from the drug reservoir portion generallyis controlled by the design of the combination of the device components,including but not limited to the materials, dimensions, surface area,preformed release ports/through-holes, and restraining plugs, as well asthe particular drug formulation and total mass of drug load, amongothers.

An example of the drug reservoir portion 78, i.e., a device body, isshown in FIG. 4. As shown, the drug reservoir portion 78 may include abody formed from an elastomeric tube 82. The tube 82 defines a reservoir60 that contains a number of drug units 158. Into the openings in theends of the tube 82, restraining plugs are inserted.

In embodiments, the drug reservoir portion 78 and drug reservoir 60operate as an osmotic pump. In such embodiments, the drug reservoirportion is formed, at least in part, from a water-permeable material. Ina preferred embodiment, the water-permeable material is silicone.Following insertion/implantation into a patient's body, water or urinepermeates through a wall of the drug reservoir portion. The water entersthe reservoir, contacts the drug formulation, forming a fluidized drug(e.g., a drug solution) which can then be dispensed at a controlled rateout of the reservoir through microchannels that form between therestraining plugs and the elastic portion of the drug reservoir portion.The delivery rate and overall performance of the osmotic pump isaffected by device parameters, such as the surface area of the drugreservoir portion; the permeability to liquid of the material used toform the drug reservoir portion; the relative dimensions, shapes, andpositions of the preformed release ports/through-holes in the devicebody; the relative dimensions, shapes, and elasticity or hardness of therestraining plugs and the elastic portion of the drug reservoir lumen;and the drug formulation dissolution profile, among other factors. Insome embodiments, the device may initially exhibit a zero-order releaserate and subsequently may exhibit a reduced, non-zero-order releaserate, in which case the overall drug release profile may be determinedby the initial zero-order release rate and the total payload.Representative examples of osmotic pump designs, and equations forselecting such designs, are described in U.S. Patent ApplicationPublication 2009/0149833 to Cima et al.

The drug reservoir portion may be formed, at least in part, from anelastomeric material, which may permit elastically deforming the devicefor its insertion into a patient, e.g., during its deployment throughdeployment instrument such as a cystoscope or catheter. For example, thetube may be elastically deformed along with the retention frame forintravesical insertion, as described in further detail below.

In one embodiment, the drug reservoir portion is formed from a materialthat is both elastomeric and water-permeable. Examples of materials thatare both elastomeric and water-permeable include silicones andthermoplastic polyurethanes known in the art. Other suitablebiocompatible materials, including inelastic biocompatible materials,also may be used.

The length, diameter, and thickness of the drug reservoir portion may beselected based on the volume of drug formulation to be contained, thedesired rate of delivery of the drug, the intended site of deployment ofthe device within the body, the desired mechanical integrity for thedevice, the desired release rate or permeability to water and urine, thedesired induction time before onset of initial release, and the desiredmethod or route of insertion into the body, among others. The tube wallthickness may be determined based on the mechanical properties and waterpermeability of the tube material, as a tube wall that is too thin maynot have sufficient mechanical integrity while a tube wall that is toothick may experience an undesirably long induction time for initial drugrelease from the device.

In one embodiment, the device body is non-resorbable. It may be formedof medical grade silicone tubing, as known in the art. Other suitablenon-resorbable materials may be used. In other embodiments, the devicebody is at least partially bioerodible. In one embodiment of abioerodible device, the drug reservoir portion is formed of abiodegradable or bioresorbable polymer. Any suitable biocompatiblepolymers may be used.

In embodiments in which the drug reservoir portion is tube-shaped, thedrug reservoir portion tube may be substantially linear and, in somecases, may be substantially cylindrical with a circular or ovalcross-section, although square, triangle, hexagon, and other polygonalcross-sectional shapes can be used, among others.

In one embodiment, the drug reservoir portion 78 has multiplereservoirs. Each reservoir may be defined by a portion of the drugreservoir inner surface and at least one partition. In embodiments inwhich the drug reservoir portion is tube-shaped, the partition may be apartition structure or plug inserted into the tube, such as a cylinder,sphere, or disk, among others, in which case the partition structure mayhave a larger cross-section than the tube, securing the partitionstructure in place and segregating adjacent reservoirs. The partitionmay be non-porous or semi-porous, non-resorbable or resorbable and maybe formed of a material described herein with reference to therestraining plugs. The partition also may be formed in the tube, such asby molding. For example, one or more webs may extend through the tubealong its length to segregate axial reservoirs that extend along thelength of the tube. The partition also may be a structure that joins twodifferent tubes that serve as separate reservoirs.

The multiple reservoirs permit segregating two or more different drugformulations in different reservoirs, delivering a single drug fromdifferent reservoirs at different rates or times following deployment,or combinations thereof. For example, two different reservoirs may be incommunication with two different restraining plugs having differentconfigurations, as described herein, which permit the drugs in the twodifferent reservoirs to be released at different rates. The twodifferent reservoirs also may house the same or different drugformulations in the same or different forms (such as liquid, semi-solid,and solid), or combinations thereof. Coatings or sheaths also may beprovided along different portions of a single drug reservoir or alongdifferent drug reservoirs housing the same or different drugformulations. The coatings or sheaths may be used to alter thewater-permeability of the water-permeable body. These embodiments can becombined and varied to achieve the desired release profile of thedesired drug.

For example, the onset of release of two doses in different reservoirscan be staged by configuring the device accordingly, such as by usingdifferent materials (e.g., materials with differentwater-permeabilities) for portions of the tube defining differentreservoirs, by placing drugs with different solubilities in thereservoirs, or by placing drugs with different forms in the reservoirs,such as a liquid form for immediate release and a solid form to besolubilized in vivo prior to release. Thus, the device may release somedrug relatively quickly after deployment while other drug may experiencean induction time before beginning release.

Preformed Release Apertures/Ports

In some embodiments, the device includes one or more ports (e.g.,apertures, orifices, slits, and the like) for dispensing the drug, suchas via generation of an osmotic pressure within the drug reservoir, asdescribed herein. The apertures may be spaced along the tube to providea passageway for release of the drug formulation. The apertures ororifices may be positioned through a sidewall of the tube. The aperturesmay be in fluid communication with one or more reservoirs (asillustrated by orifice 66 in FIGS. 2 and 3A) or may be adjacent arestraining plug (as illustrated by ports 68 in FIGS. 9 and 10), asdescribed herein.

An embodiment of an aperture 66 is shown on the drug reservoir portion78 in FIG. 3A. The aperture 66 may be located about a middle of the drugreservoir portion 78 or adjacent to an end of the drug reservoir 60,which may affect the ease of loading solid drug units 158 into the drugreservoir portion 78 as described below. The apertures may be positionedaway from a portion of the tube that will be folded during insertion tolimit tearing of degradable membranes on the apertures.

The size, number, and placement of the apertures may be selected toprovide a controlled rate of release of the drug. A device that operatesprimarily as an osmotic pump may have one or more apertures sized smallenough to reduce diffusion of the drug through the aperture(s), yetlarge enough and spaced appropriately along the tube to reduce thebuildup of hydrostatic pressure in the tube. Within these constraints,the size and number of apertures for a single device (or reservoir) canbe varied to achieve a selected release rate. In exemplary embodiments,the diameter of the aperture is between about 20 μm and about 500 μm,such as between about 25 μm and about 300 μm, and more particularlybetween about 30 μm and about 200 μm. In one particular example, theaperture has a diameter between about 100 μm and about 200 μm, such asabout 150 μm. In one particular example, the aperture has a diameterbetween about 25 μm and about 100 μm, such as about 75 μm. A singledevice may have apertures of two or more different sizes. The aperturemay be circular, although other shapes are possible and envisioned, withthe shape typically depending on manufacturing considerations. Examplesof processes for forming the apertures include mechanical punching,laser drilling, laser ablation, and molding. The aperture may slightlytaper from an exterior to an interior of the tube, and the aperture maybe created either before or after the drug is loaded into the tube.

In some embodiments, as shown in FIG. 10, the preformed release port 68is a slit in the device body 52, which is configured to provide anoutlet for the drug 58 upon generation of a pressure sufficient tostretch the elastic portion 54 of the body 52 in which the port 68 isformed to open the slit and thereby provide a through-hole for the drugsolution. Such a slit may be configured to function as a one-way valve,permitting release out from the device when opened by internal pressureand otherwise remaining closed so that external fluids do not pass intothe device.

Restraining Plugs

The restraining plugs 56 may have any shape suitable for placement inthe one or more elastic portions 54 of the body 52 that permits theformation of microchannels 62 as described herein. In embodiments, therestraining plugs 56 are cylindrical or substantially cylindrical. Asused herein, the term “substantially cylindrical” refers to any shapethat is non-polygonal when viewed in cross-section. In otherembodiments, the restraining plugs are partially cylindrical orsubstantially cylindrical, and have at least one portion that is wedged,tapered, angled, or rounded. In embodiments, the restraining plugs aresolid, not hollow.

FIG. 5 depicts a series of restraining plugs 502, 503, 504, 505, and 506having different shapes. FIG. 6 depicts the restraining plugs 502, 503,504, 505, and 506 inserted into a tube-shaped elastic portion 501 of adevice body. When the restraining plug has a wedged, tapered, angled, orrounded surface, these surfaces may allow the microchannels describedherein to form more easily. Not wishing to be bound by any particulartheory, it is believed that the wedged, tapered, angled, or roundedsurfaces may provide a preferential path for osmotic flow along or nearsuch surfaces. As a result, less hydrostatic pressure may be required tocreate one or more microchannels between the restraining plug and theelastic portion of the water-permeable body. Generally, the restrainingplugs may have one or more wedged, tapered, angled, or rounded surfaceson one side or both sides of the restraining plugs' longitudinal axis.In embodiments, the angle between the longitudinal surface of therestraining plug and the surface of the wedged, tapered, angled, orrounded portion may be from about 30° to about 60°.

As shown in FIG. 6, the wedged, tapered, angled, or rounded surfaces ofthe restraining plugs 502, 503, 504, 505, 506 can be inserted into theend of the tube-shaped elastic portion 501 so that the wedged, tapered,angled, or rounded surfaces of the restraining plugs are incommunication with the interior (drug reservoir) of the drug deliverydevices. In FIG. 6, the opposed base of the restraining plugs facesoutward, as an exterior surface of the drug delivery devices.Alternatively, in other embodiments, the position may be reversed, sothat the wedged, tapered, angled, or rounded surfaces of the restrainingplug face outward, as an exterior surface of the drug delivery devices,while the base of the restraining plug is in communication with theinterior (drug reservoir) of the drug delivery devices. In thisposition, the wedged, tapered, angled, or rounded surfaces of therestraining plugs may create a void space at or near the end of theelastic portion. The void space or a portion thereof may host anadhesive, clamp, plug, or other known means for securing the restrainingplug, as illustrated in FIGS. 3A-3C.

In certain embodiments, the elastic portion of the body and therestraining plug may be disposed at a location of the device other thanat the terminal end.

The restraining plugs 56 should contact the elastic portions 54 of thewater-permeable body 52 in a manner that prohibits the restraining plug56 from being expelled from the elastic portion 54 when the device 50 iscompressed in the body after deployment and/or when a hydrostatic forceis exerted on the restraining plug 56. In embodiments, the restrainingplug 56 and the elastic portion 54 are secured together by aninterference fit, e.g., by frictional engagement, with one another,alone or optionally with the aid of an adhesive. The restraining plug 56should remain in the elastic portion 54 of the water-permeable body 52when the device 50 is elastically deformed between its retention shapeand relatively straightened shape.

In a preferred embodiment, the restraining plugs 56 do not migratewithin the elastic portions 54 of the device body 52 after deploymentand during drug release. In other embodiments, the restraining plugs 56do migrate within the elastic portions 54 of the water-permeable body 52after deployment and during drug release. Migration of the restrainingplugs 56 can be tolerated as long as the drug release is not undesirablyaffected.

In embodiments, the cross-sectional shape of the restraining plugs 56substantially conforms to the inner dimensions of the elastic portion 54of the device body 52. In other embodiments, the outer diameter of therestraining plugs 56 exceeds the inner diameter of the elastic portion54 of the device body 52. The phrase “inner diameter,” as used herein,is not intended to imply that the elastic portion is always circularwhen viewed in cross-section; instead, the term refers to the largestdiameter or major axis of the lumen of the elastic portion of thewater-permeable body. Similarly, the phrase “outer diameter,” as usedherein, is not intended to imply that the restraining plug, when viewedin cross-section, is always circular; instead, the term refers to thelargest diameter or major axis of the cross-section of the restrainingplug or its base.

In one embodiment, the outer diameter of the restraining plug exceedsthe inner diameter of the elastic portion of the device body by at least3 percent. In another embodiment, the outer diameter of the restrainingplug exceeds the inner diameter of the elastic portion of the devicebody by at least 5 percent. In yet another embodiment, the outerdiameter of the restraining plug exceeds the inner diameter of theelastic portion of the device body by at least 10 percent. In a furtherembodiment, the outer diameter of the restraining plug exceeds the innerdiameter of the elastic portion of the device body by at least 15percent. In a still further embodiment, the outer diameter of therestraining plug exceeds the inner diameter of the elastic portion ofthe device body by at least 20 percent. In a particular embodiment, theouter diameter of the restraining plug exceeds the inner diameter of theelastic portion of the body by at least 25 percent.

In one embodiment, the outer diameter of the restraining plug exceedsthe inner diameter of the elastic portion of the device body by about 5percent, and the inner diameter of the elastic portion of the devicebody is between 2.1 and 2.2 mm, (e.g., 2.16 mm) and the outer diameterof the restraining plug is between 2.2 and 2.3 mm (e.g., 2.27 mm). Therestraining plug, in this embodiment, has a length of from about 2.5 mmto about 5 mm.

In another embodiment, the outer diameter of the restraining plugexceeds the inner diameter of the elastic portion of the water-permeablebody by about 28 percent. For example, in one case, the inner diameterof the elastic portion of the water-permeable body is between 2.1 and2.2 mm (e.g., 2.16 mm), and the outer diameter of the restraining plugis between 2.7 and 2.8 mm (e.g., 2.77 mm). The restraining plug, in thisembodiment, has a length of from about 2.5 mm or 5 mm long.

The restraining plugs may be of any length that is suited for allowingthe formation of microchannels between the restraining plug and theelastic portion of the device body. The outer surface of the restrainingplug may contact the inner surface of the elastic portion of the devicebody along the entire length of the restraining plug or for only aportion of the restraining plug's length. For example, the outer surfaceof a restraining plug shaped like a cylinder may contact the innersurface of the opening in the elastic portion of the water-permeablebody along the entire length of the restraining plug. The outer surfaceof a restraining plug having one or more wedged, angled, or taperedsurfaces, however, may only contact the inner surface of the elasticportion of the water-permeable body along a portion of the restrainingplug's overall length, as shown, for example, in FIGS. 3 and 6.

In embodiments, the length of the restraining plug may be from about 2mm to about 10 mm, from about 2 mm to about 8 mm, from about 2 to about6 mm, or from about 2.5 mm to about 5 mm.

Generally, the inner surface of the elastic portion of thewater-permeable body and the restraining plug may be shaped so that therestraining plug and the elastic portion of the water-permeable bodyremain in contact with each other during deployment. In someembodiments, as shown in FIG. 3, adhesive 70 may be used to securetogether the elastic portion 54 of the water-permeable body 52 and therestraining plug 56. A single portion or one or more discrete portionsof adhesive may be used as long as the amount and placement of adhesivedoes not undesirably impact the drug release as described herein. Inother embodiments, the restraining plug may be secured mechanically. Forexample, an external clamp may be used to secure together the elasticportion of the water-permeable body and the restraining plug. Anysuitable clamp may be used as long as it does not undesirably impacttolerability of the device to the patient or the drug release asdescribed herein. When the restraining plug is secured mechanically,with adhesive, or both, it may be necessary to form the elastic portionor the restraining plug or both with a softer material to ensure theformation of microchannels.

The restraining plugs may be made from any biocompatible material orcombination of biocompatible materials that permits the release of drugfrom the device as described herein. For example, the restraining plugsmay be made from a polymer, such as silicone or ethylene vinyl acetate,a ceramic, an adhesive, or a combination thereof.

In certain embodiments, the restraining plugs are coated with a materialto inhibit undesired bonding between the inner surface of the elasticportion and the restraining plug, such as may occur with certainpolymeric materials when the assembled device is sterilized, e.g., bygamma irradiation. For example, the restraining plugs may be siliconeand coated with parylene, such as parylene C.

The Retention Frame Portion

In a preferred embodiment, as shown in FIGS. 3 and 4, the drug deliverydevice 50 includes a retention frame portion 76. The retention frameportion 76 is associated with the drug reservoir portion 78 and permitsretaining the drug reservoir portion 78 in the body, such as in thebladder. The retention frame portion 76 may include a retention frame 74that is deformable between a relatively expanded shape and a relativelylower-profile shape. For example, the retention frame 74 may naturallyassume the relatively expanded shape, may be manipulated into therelatively lower-profile shape for insertion into the body, and mayspontaneously return to the relatively expanded shape upon insertioninto the body. The retention frame 74 in the relatively expanded shapemay be shaped for retention in a body cavity, and the retention frame 74in the relatively lower-profile shape may be shaped for insertion intothe body through the working channel of a deployment instrument such asa catheter or cystoscope. To achieve such a result, the retention frame74 may have an elastic limit, modulus, and/or spring constant selectedto impede the device from assuming the relatively lower-profile shapeonce deployed. Such a configuration may limit or prevent accidentalexpulsion of the device from the body under expected forces. Forexample, the device may be retained in the bladder during urination orcontraction of the detrusor muscle.

In a preferred embodiment, the retention frame 74 includes or consistsof an elastic wire. For example, in the embodiment shown in FIGS. 3 and4, the retention frame 74 is an elastic wire formed from a superelasticalloy, such as nitinol, and surrounded by the wall 84 of the retentionframe lumen 80, which forms a protective sheath about the retentionframe 74. The wall 84 may be formed from a polymer material, such assilicone. In some other embodiments, the retention frame may be anelastic wire formed from a superelastic alloy, such as nitinol, that iscovered in a polymer coating such as a silicone sheath and is attachedto the drug reservoir portion. In still other embodiments, the elasticwire may be formed of a relatively low modulus elastomer.

In some embodiments, the retention frame lumen 80 may include theretention frame 74 and a filling material, such as a polymer filling. Anexample filling material is a silicone adhesive, such as MED3-4213 byNusil Technology LLC, although other filling materials may be used. Thefilling material may completely or partially fill the void in theretention frame lumen 80 about the retention frame 74. For example, thefilling material may be poured into the retention frame lumen 80 aboutthe retention frame 74 and may cure therein. The filling material mayreduce the tendency of the drug reservoir lumen 60 to stretch along, ortwist or rotate about, the retention frame 74, while maintaining thedrug reservoir lumen 60 in a selected orientation with reference to theretention frame 74. The filling material is not necessary, however, andmay be omitted.

When the retention frame 74 is in the relatively expanded shape, such asthe coiled shape shown in FIG. 3A, the device 50 may occupy a spacehaving dimensions suited to impede expulsion from the bladder. When theretention frame is in the relatively lower-profile shape, such as theelongated shape shown in FIG. 7, the device 700 may occupy a spacesuited for insertion into the body, such as through the working channelof a deployment instrument 702. The properties of the elastic wire causethe device to function as a spring, deforming in response to acompressive load but spontaneously returning to its initial shape oncethe load is removed.

A retention frame that assumes a pretzel shape may be relativelyresistant to compressive forces. The pretzel shape essentially comprisestwo sub-circles, each having its own smaller arch and sharing a commonlarger arch. When the pretzel shape is first compressed, the larger archabsorbs the majority of the compressive force and begins deforming, butwith continued compression the smaller arches overlap, and subsequently,all three of the arches resist the compressive force. The resistance tocompression of the device as a whole increases once the two sub-circlesoverlap, impeding collapse and voiding of the device as the bladdercontracts during urination.

In embodiments in which the retention frame comprises a shape-memorymaterial, the material used to form the frame may “memorize” andspontaneously assume the relatively expanded shape upon the applicationof heat to the device, such as when exposed to body temperatures uponentering the bladder.

The retention frame may be in a form having a high enough springconstant to retain the device within a body cavity, such as the bladder.A high modulus material may be used, or a low modulus material.Especially when a low-modulus material is used, the retention frame mayhave a diameter and/or shape that provides a spring constant withoutwhich the frame would significantly deform under the forces ofurination. For example, the retention frame may include one or morewindings, coils, spirals, or combinations thereof, specifically designedto achieve a desirable spring constant as described in U.S. ApplicationPublication 2009/0149833 to Cima et al.

The retention frame may have a two-dimensional structure that issubstantially confined to a plane, a three-dimensional structure, suchas a structure that occupies the interior of a spheroid, or somecombination thereof.

Drug Formulations

The term “drug” as used herein encompasses any suitable pharmaceuticallyactive ingredient. The drug may be small molecule, macromolecule,biologic, or metabolite, among other forms/types of active ingredients.The drug described herein includes its alternative forms, such as saltforms, free acid forms, free base forms, and hydrates. The drug may beformulated with one or more pharmaceutically acceptable excipients knownin the art. Non-limiting examples of the drug include gemcitabine,oxaliplatin, and/or another chemotherapeutic agent; trospium and/oranother antimuscarinic agent; and/or lidocaine and/or another anestheticagent. In one embodiment, the first compartment may be loaded with twoor more types of drug tablets (e.g., different drugs), so that acombination of drugs may be delivered.

In embodiments, the drug is one used to treat pain. A variety ofanesthetic agents, analgesic agents, and combinations thereof may beused. In one embodiment, the drug is an anesthetic agent. The anestheticagent may be a cocaine analogue. The anesthetic agent may be anaminoamide, an aminoester, or combinations thereof. Representativeexamples of aminoamides or amide-class anesthetics include articaine,bupivacaine, carticaine, cinchocaine, etidocaine, levobupivacaine,lidocaine, mepivacaine, prilocalne, ropivacaine, and trimecaine.Representative examples of aminoesters or ester-class anestheticsinclude amylocalne, benzocaine, butacaine, chloroprocaine, cocaine,cyclomethycaine, dimethocaine, hexylcaine, larocaine, meprylcaine,metabutoxycaine, orthocaine, piperocaine, procaine, proparacaine,propoxycaine, proxymetacaine, risocaine, and tetracaine. The drug alsocan be an antimuscarinic compound that exhibits an anesthetic effect,such as oxybutynin or propiverine. In embodiments, the analgesic agentincludes an opioid. Representative examples of opioid agonists includealfentanil, allylprodine, alphaprodine, anileridine, benzyl morphine,bezitramide, buprenorphine, butorphanol, clonitazene, codeine,desomorphine, dextromoramide, dezocine, diampromide, diamorphone,dihydrocodeine, dihydromorphine, dimenoxadol, dimepheptanol, dimethylthiambutene, dioxaphetyl butyrate, dipipanone, eptazocine,ethoheptazine, ethylmethylthiambutene, ethylmorphine, etonitazenefentanyl, heroin, hydrocodone, hydromorphone, hydroxypethidine,isomethadone, ketobemidone, levorphanol, levophenacylmorphan,lofentanil, meperidine, meptazinol, metazocine, methadone, metopon,morphine, myrophine, nalbuphine, narceine, nicomorphine, norlevorphanol,normethadone, nalorphine, normorphine, norpipanone, opium, oxycodone,oxymorphone, papavereturn, pentazocine, phenadoxone, phenomorphan,phenazocine, phenoperidine, piminodine, piritramide, proheptazine,promedol, properidine, propiram, propoxyphene, sufentanil, tilidine,tramadol, pharmaceutically acceptable salts thereof, and mixturesthereof. Other opioid drugs, such as mu, kappa, delta, and nociceptionopioid receptor agonists, are contemplated. Representative examples ofother suitable pain relieving agents include such agents as salicylalcohol, phenazopyridine hydrochloride, acetaminophen, acetylsalicylicacid, flufenisal, ibuprofen, indoprofen; indomethacin, naproxen.

In certain embodiments, the drug is one used to treat inflammatoryconditions such as interstitial cystitis, radiation cystitis, painfulbladder syndrome, prostatitis, urethritis, post-surgical pain, andkidney stones. Non-limiting examples of drugs for these conditionsinclude lidocaine, glycosaminoglycans (e.g., chondroitin sulfate,sulodexide), pentosan polysulfate sodium (PPS), dimethyl sulfoxide(DMSO), oxybutynin, mitomycin C, heparin, flavoxate, ketorolac, or acombination thereof. Other non-limiting examples of drugs that may beused in the treatment of IC include nerve growth factor monoclonalantibody (MAB) antagonists, such as Tanezumab, and calcium channelalpha-2-delta modulators, such as PD-299685 or gabepentin.

In certain embodiments, the drug is one used to treat urinaryincontinence, frequency, or urgency, including urge incontinence andneurogenic incontinence, as well as trigonitis. Drugs that may be usedinclude anticholinergic agents, antispasmodic agents, anti-muscarinicagents, □-2 agonists, alpha adrenergics, anticonvulsants, norepinephrineuptake inhibitors, serotonin uptake inhibitors, calcium channelblockers, potassium channel openers, and muscle relaxants.Representative examples of suitable drugs for the treatment ofincontinence include oxybutynin, S-oxybutylin, emepronium, verapamil,imipramine, flavoxate, atropine, propantheline, tolterodine, rociverine,clenbuterol, darifenacin, terodiline, trospium, hyoscyamin, propiverine,desmopressin, vamicamide, clidinium bromide, dicyclomine HCl,glycopyrrolate aminoalcohol ester, ipratropium bromide, mepenzolatebromide, methscopolamine bromide, scopolamine hydrobromide, iotropiumbromide, fesoterodine fumarate, YM-46303 (Yamanouchi Co., Japan),lanperisone (Nippon Kayaku Co., Japan), inaperisone, NS-21 (NipponShinyaku Orion, Formenti, Japan/Italy), NC-1800 (Nippon Chemiphar Co.,Japan), Z D-6169 (Zeneca Co., United Kingdom), and stilonium iodide.

In certain embodiments, the drug is one used to treat urinary tractcancer, such as bladder cancer and prostate cancer. Drugs that may beused include antiproliferative agents, cytotoxic agents,chemotherapeutic agents, or a combination thereof. Representativeexamples of drugs which may be suitable for the treatment of urinarytract cancer include Bacillus Calmette Guerin (BCG) vaccine, cisplatin,doxorubicin, valrubicin, gemcitabine, mycobacterial cell wall-DNAcomplex (MCC), methotrexate, vinblastine, thiotepa, mitomycin,fluorouracil, leuprolide, diethylstilbestrol, estramustine, megestrolacetate, cyproterone, flutamide, a selective estrogen receptormodulators (i.e. a SERM, such as tamoxifen), botulinum toxins, andcyclophosphamide. The drug may be a biologic, and it may comprise amonoclonal antibody, a TNF inhibitor, an anti-leukin, or the like. Thedrug also may be an immunomodulator, such as a TLR agonist, includingimiquimod or another TLR7 agonist. The drug also may be a kinaseinhibitor, such as a fibroblast growth factor receptor-3(FGFR3)-selective tyrosine kinase inhibitor, a phosphatidylinositol 3kinase (PI3K) inhibitor, or a mitogen-activated protein kinase (MAPK)inhibitor, among others or combinations thereof. Other examples includecelecoxib, erolotinib, gefitinib, paclitaxel, polyphenon E, valrubicin,neocarzinostatin, apaziquone, Belinostat, Ingenol mebutate, Urocidin(MCC), Proxinium (VB 4845), BC 819 (BioCancell Therapeutics), Keyholelimpet haemocyanin, LOR 2040 (Lorus Therapeutics), urocanic acid, OGX427 (OncoGenex), and SCH 721015 (Schering-Plough). Other intravesicalcancer treatments include small molecules, such as Apaziquone,adriamycin, AD-32, doxorubicin, docetaxel, epirubicin, gemcitabine,HTI-286 (hemiasterlin analogue), idarubicin, γ-linolenic acid,mitozantrone, meglumine, and thiotepa; large molecules, such asActivated macrophages, activated T cells, EGF-dextran, HPC-doxorubicin,IL-12, IFN-a2b, IFN-γ, α-lactalbumin, p53 adenovector, TNFα;combinations, such as Epirubicin+BCG, IFN+farmarubicin, Doxorubicin+5-FU(oral), BCG+IFN, and Pertussis toxin+cystectomy; activated cells, suchas macrophages and T cells; intravesical infusions such as IL-2 andDoxorubicin; chemosensitizers, such as BCG+antifirinolytics(paramethylbenzoic acid or aminocaproic acid) and Doxorubicin+verapimil;diagnostic/imaging agents, such as Hexylaminolevulinate,5-aminolevulinic acid, Iododexyuridine, HMFG1 Mab+Tc99m; and agents forthe management of local toxicity, such as Formaline (hemorrhagiccystitis).

In certain embodiments, the drug is one used to treat infectionsinvolving the bladder, the prostate, and the urethra. Antibiotics,antibacterial, antifungal, antiprotozoal, antiseptic, antiviral andother antiinfective agents can be administered for treatment of suchinfections. Representative examples of drugs for the treatment ofinfections include mitomycin, ciprofloxacin, norfloxacin, ofloxacin,methanamine, nitrofurantoin, ampicillin, amoxicillin, nafcillin,trimethoprim, sulfonamides trimethoprimsulfamethoxazole, erythromycin,doxycycline, metronidazole, tetracycline, kanamycin, penicillins,cephalosporins, and aminoglycosides.

In certain embodiments, the drug is one used to treat fibrosis of agenitourinary site, such as the bladder or uterus. Representativeexamples of drugs for the treatment of fibroids include pentoxphylline(xanthine analogue), antiTNF, antiTGF agents, GnRH analogues, exogenousprogestins, antiprogestins, selective estrogen receptor modulators,danazol and NSAIDs. In certain embodiments, the drug is one used totreat neurogenic bladder. Representative examples of such drugs includeanalgesics or anaesthetics, such as lidocaine, bupivacaine, mepivacaine,prilocalne, articaine, and ropivacaine; anticholinergics;antimuscarinics such as oxybutynin or propiverine; a vanilloid, such ascapsaicin or resiniferatoxin; antimuscarinics such as ones that act onthe M3 muscarinic acetylcholine receptor (mAChRs); antispasmodicsincluding GABA_(B) agonists such as baclofen; botulinum toxins;capsaicins; α-adrenergic antagonists; anticonvulsants; serotoninreuptake inhibitors such as amitriptyline; and nerve growth factorantagonists. In various embodiments, the drug may be one that acts onbladder afferents or one that acts on the efferent cholinergictransmission, as described in Reitz et al., Spinal Cord 42:267-72(2004).

In certain embodiments, the drug is one used to treat incontinence dueto neurologic detrusor overactivity and/or low compliant detrusor.Examples of these types of drugs include bladder relaxant drugs (e.g.,oxybutynin (antimuscarinic agent with a pronounced muscle relaxantactivity and local anesthetic activity), propiverine, impratroprium,tiotropium, trospium, terodiline, tolterodine, propantheline,oxyphencyclimine, flavoxate, and tricyclic antidepressants; drugs forblocking nerves innervating the bladder and urethra (e.g., vanilloids(capsaicin, resiniferatoxin), botulinum-A toxin); or drugs that modulatedetrusor contraction strength, micturition reflex, detrusor sphincterdyssynergia (e.g., GABAb agonists (baclofen), benzodiazapines). Inanother embodiment, the drug is selected from those known for thetreatment of incontinence due to neurologic sphincter deficiency.Examples of these drugs include α-adrenergic agonists, estrogens,β-adrenergic agonists, tricyclic antidepressants (imipramine,amitriptyline). In still another embodiment, the drug is selected fromthose known for facilitating bladder emptying (e.g., α-adrenergicantagonists (phentolamitie) or cholinergics). In yet another embodiment,the drug is selected from among anticholinergic drugs (e.g.,dicyclomine), calcium channel blockers (e.g., verapamil) tropanealkaloids (e.g., atropine, scopolamine), nociceptin/orphanin FQ, andbethanechol (e.g., M3 muscarinic agonist, choline ester).

In some embodiments, an agent that increases the osmotic pressure may bedisposed in the water-permeable body or included in the drug formulationor, in some embodiments, the drug itself may act as an osmotic agent.For example, the drug and osmotic agent can be homogeneously mixed orcompressed into tablets. As another example, a drug tablet may bedisposed near a restraining plug, and an osmotic agent can be arrangednext to the drug tablet. Non-limiting examples of osmotic agents includeurea, citric acid, L-tartaric acid, lactose-fructose, dextrose-fructose,sucrose-fructose, mannitol-fructose, sodium chloride, fructose,lactose-sucrose, potassium chloride, lactose-dextrose,mannitol-dextrose, dextrose-sucrose, mannitol-sucrose, sucrose,mannitol-lactose, dextrose, potassium sulfate, mannitol, sodiumphosphate tribase.12 H₂O, sodium phosphate dibasic.7 H₂O, sodiumphosphate dibasic anhydrous, and sodium phosphate monobasic.H₂O.

Use and Applications of the Device

The device may be deployed in a body cavity or lumen, and subsequentlymay release one or more drugs for the treatment of one or moreconditions, locally to one or more tissues at the deployment site and/orregionally to other tissues distal from the deployment site. The releasemay be controlled over an extended period. Thereafter, the device may beremoved, resorbed, excreted, or some combination thereof.

In one example, the device is inserted into the body by passing the drugdelivery device through a deployment instrument and releasing the devicefrom the deployment instrument into the body. In cases in which thedevice is deployed into a body cavity such as the bladder, the deviceassumes a retention shape, such as an expanded or higher profile shape,once the device emerges from the deployment instrument into the cavity.An example is illustrated in FIG. 7, which shows the device 700 assuminga retention shape as the device exits a deployment instrument 702. Thedeployment instrument 702 may be any suitable lumen device, such as acatheter, urethral catheter, or cystoscope. The deployment instrument702 may be a commercially available device or a device specially adaptedfor the present drug delivery devices, for example, as described in U.S.Patent Application Publication 2011/0202036 to Boyko et al.

Once inserted into the body, the device releases the drug in acontrolled manner. The device may provide extended, continuous,intermittent, or periodic release of a desired quantity of drug over adesired, predetermined time period. In embodiments, the device candeliver the desired dose of drug over an extended period, such as 12hours, 24 hours, 5 days, 7 days, 10 days, 14 days, or 20, 25, 30, 45,60, or 90 days, or more. In a preferred embodiment, the device is anintravesical drug delivery device, which releases a therapeutic amountof a drug continuously into urine in the bladder over a selectedtreatment period ranging from 7 days to 60 days, e.g., from 14 days to30 days. The rate of delivery and dosage of the drug can be selecteddepending upon the drug being delivered and the disease or conditionbeing treated.

In embodiments in which the device comprises a drug in a solid form,elution of drug from the device occurs following dissolution of the drugwithin the device. Bodily fluid enters the device, contacts the drug andsolubilizes the drug, and thereafter the dissolved drug exits the devicevia the microchannels described herein. For example, the drug may besolubilized upon contact with urine in cases in which the device isdeployed in the bladder.

Subsequently, the device may be retrieved from the body, such as incases in which the device is non-resorbable, non-collapsible, orotherwise needs to be removed.

The device also may be configured to be completely or partiallybioresorbable, such that retrieval is unnecessary. In one case, thedevice is resorbed or sufficiently degraded that it can be expelled fromthe bladder during urination. In some embodiments, the device includebiodegradable links such that the device can collapse into a shape thatpermits passage through the urethra during urination, as described inU.S. Pat. No. 8,690,840 to Lee et al., which is incorporated herein byreference. The device may not be retrieved or resorbed until some of thedrug, or preferably most or the entire drug, has been released.

FIG. 8 illustrates the deployment of a device 800 into the bladder,wherein the adult human male anatomy is shown by way of example. Adeployment instrument 802 may be inserted through the urethra to thebladder, and the device 800 may be passed through the deploymentinstrument 802, driven by a stylet and/or a flow of lubricant or otherfluid, for example, until the device 800 exits into the bladder. Thus,the device is deployed into the bladder of a male or female humanpatient in need of treatment.

The device may be deployed into the bladder of a patient in anindependent procedure or in conjunction with another urological or otherprocedure or surgery, either before, during, or after the otherprocedure. The device may release one or more drugs that are deliveredto local and/or regional tissues for therapy or prophylaxis, eitherperi-operatively, post-operatively, or both.

In one embodiment, the drug delivery device, with a self-contained drugpayload, is deployed wholly within the bladder to provide sustaineddelivery of at least one drug to the bladder in an amount that istherapeutically effective for the target tissue in need of treatment. Itmay be the bladder itself or regionally proximate to the bladder. Suchregional delivery may provide an alternative to systemic administration,which may entail undesirable side effects or result in insufficientbioavailability of the drug. Following in vivo deployment of the device,at least a portion of the payload of drug is released from the devicesubstantially continually over an extended period, to the urothelium andpossibly to nearby tissues, in an amount effective to provide treatmentor to improve bladder function in the patient. In a preferredembodiment, the device resides in the bladder releasing the drug over apredetermined period, such as two weeks, three weeks, four weeks, amonth, or more.

In such cases, the device may be used to treat interstitial cystitis,radiation cystitis, pelvic pain, overactive bladder syndrome, bladdercancer, neurogenic bladder, neuropathic or non-neuropathicbladder-sphincter dysfunction, infection, post-surgical pain or otherdiseases, disorders, and conditions treated with drugs delivered to thebladder. The device may deliver drugs that improve bladder function,such as bladder capacity, compliance, and/or frequency of uninhibitedcontractions, that reduce pain and discomfort in the bladder or othernearby areas, or that have other effects, or combinations thereof. Thebladder-deployed device also may deliver a therapeutically effectiveamount of one or more drugs to other genitourinary sites within thebody, such as other locations within urological or reproductive systemsof the body, including one or both of the kidneys, the urethra, one orboth of the ureters, the penis, the testes, one or both of the seminalvesicles, one or both of the vas deferens, one or both of theejaculatory ducts, the prostate, the vagina, the uterus, one or both ofthe ovaries, or one or both of the fallopian tubes, among others orcombinations thereof. For example, the intravesical drug delivery devicemay be used in the treatment of kidney stones or fibrosis, erectiledysfunction, among other diseases, disorders, and conditions.

In one embodiment, the intravesical drug delivery device is deployedinto a bladder to locally deliver lidocaine or another anesthetic agentfor management of pain arising from any source, such as a disease ordisorder in genitourinary tissues, or pain stemming from any bladderprocedure, such as surgery, catheterization, ablation, medical deviceimplantation, or stone or foreign object removal, among others.

In embodiments, the drug delivery device is sterilized, such as afterthe device is manufactured/assembled and before the device is deployedinto the patient. In some cases, the device may be sterilized after thedevice is packaged, such as by subjecting the package to gammairradiation, electron beam irradiation, or ethylene oxide gas. Althoughgamma irradiation may affect the performance of certain aspects of thedrug delivery devices, materials and configurations can be chosen, asexplained herein, to eliminate or substantially neutralize any adverseeffects.

In one aspect, a method of administering a drug to a patient includesinserting any of the drug delivery devices described herein into a lumenor body cavity of a patient; and permitting water influx into thereservoir to develop a pressure in the reservoir effective to cause thedrug to flow from the reservoir through any preformed through-holespresent in the device body and through one or more microchannels formedbetween the restraining plug and the elastic portion of the device bodyfrom (i) the drug reservoir and at least one preformed release port or(ii) the drug reservoir and an opening at the end of the device, and outof the device and into the lumen or body cavity. In certain embodiments,the body cavity is the bladder of the patient.

In some particular embodiments, trospium is locally administered intothe bladder of a patient for the treatment of neurogenic detrusoroveractivity (NDO) resulting from a spinal cord injury (SCI). In someembodiments, the patient is one who has been diagnosed to have traumaticor nontraumatic suprasacral SCI for longer than 6 months and adocumented history of NDO. Such a patient may also need to use anintravesical catheter (non-indwelling) to empty his or her bladder. Insome of these embodiments, the local administration of the trospium intothe urinary bladder of the patient is accomplished using one of the drugdelivery systems described herein. In some particular embodiments, thedevice (containing a payload of trospium, e.g., tablets comprisingtrospium chloride) is placed into the bladder through an inserter andthen the device is removed 30 to 60 days later, such as 42 days later.The device releases the trospium gradually, continuously, during theindwelling time. In some of these embodiments, the device releasestrospium at a daily average rate of from about 2 mg/day to about 30mg/day, for example from about 5 mg/day to about 25 mg/day, such as fromabout 5 mg/day to about 15 mg/day, or about 10 mg/day, over thetreatment period, e.g., over a 42-day indwelling time. In some otherembodiments, the trospium may be locally administered into the urinarybladder by other delivery systems known in the art, for example asdescribed in U.S. Patent Application Publication No. 2015/0182516 toGiesing, which is incorporated herein by reference.

In some particular embodiments, trospium is locally administered intothe bladder of a patient for the treatment of idiopathic overactivebladder (iOAB) and urinary incontinence. In some embodiments, thepatient is one who has been diagnosed to have symptoms of OAB(frequency/urgency) with urge urinary incontinence or mixed urinaryincontinence with a predominant urge component for at least 6 months. Insome of these embodiments, the local administration of the trospium intothe urinary bladder of the patient is accomplished using one of the drugdelivery systems described herein. In some particular embodiments, thedevice (containing a payload of trospium, e.g., tablets comprisingtrospium chloride) is placed into the bladder through an inserter andthen the device is removed 30 to 60 days later, such as 42 days later.The device releases the trospium gradually, continuously, during theindwelling time. In some of these embodiments, the device releasestrospium at a daily average rate of from about 2 mg/day to about 30mg/day, for example from about 5 mg/day to about 25 mg/day, such as fromabout 5 mg/day to about 15 mg/day, or about 10 mg/day, over thetreatment period, e.g., over a 42-day indwelling time. In some otherembodiments, the trospium may be locally administered into the urinarybladder by other delivery systems known in the art, for example asdescribed in U.S. Patent Application Publication No. 2015/0182516 toGiesing, which is incorporated herein by reference.

The present invention may be further understood with reference to thefollowing non-limiting examples.

Example 1

Prototypes of devices having a central laser-drilled orifice weremanufactured and loaded with trospium chloride tablets. One set of thedevices included two spacer orifices (i.e., plugs having longitudinalorifices formed therein) at each end, with the second set of deviceshaving two restraining plugs at the ends. Illustrations of theprototypes are shown at FIGS. 11 and 12. The device of FIG. 11 has threedrug release apertures: two at the opposing ends and one in thesidewall. The device had a drug reservoir lumen inner diameter of 2.64mm and a wall thickness of 0.2 mm. The wall had a durometer of 50A. Thedevice of FIG. 12 has one release aperture plus two opposing endscapable of providing release upon sufficient osmotic pressure to formmicrochannels. The device had a drug reservoir lumen inner diameter of2.64 mm and a wall thickness of 0.2 mm. The wall had a durometer of 50A.

The devices were placed in containers of deionized water and the amountof trospium chloride released over time was measured. Results of invitro tests (five for each prototype design) are shown in the graphs ofFIGS. 11 and 12. As can be seen, the restraining plugs achieve aconsistent, reproducible release profile, as compared to the lessreproducible release profile of the spacer orifice device. The observeddifference between the two systems was not predictable.

Example 2

The device illustrated in FIG. 3 was manufactured as follows. The devicewas a dual lumen silicone tube with a laser-machined orifice, parylene Ccoated silicone elastomer plugs to contain the drug as well as to formone-way valve at each end of the drug compartment in the drug lumen, andwhite silicone adhesive in the large lumen to hold the plugs in place, apre-formed superelastic nitinol wireform housed in the retention framelumen, and retention lumen ends sealed with translucent siliconeadhesive. The drug was formed as tablets containing trospium chloride(pharmaceutical active ingredient), povidone (polyvinylpyrrolidone(PVP)) K29/32 (a binding agent excipient), and polyethylene glycol 8000(a lubricant excipient). Each device contained 850 mg of trospiumchloride. The device is small in size (less than 5 cm on the long axis),flexible, and contoured, in order to minimize potential irritation andinflammation. The drug reservoir lumen had an inner diameter of 2.64 mmand a wall thickness of 0.41 mm. The nitinol wire had a thickness of0.279 mm.

The device body serves as an osmotic pump and provides passivecontrolled release of the drug when filled with drug while the nitinolwireform provides bladder retention of the system during a treatmentperiod while the system remains free-moving in the bladder. The device,as an osmotic pump, delivers the therapeutic agent at a controlled rateby osmosis. The silicone tube wall housing the trospium mini-tabletsacts as a semipermeable membrane, and the thickness of the wall canmodulate water flux into the system and eventually control the drugrelease rate. There are multiple drug release channels in the system;one in the middle of the system, and the others are at the ends. Therate of drug delivery is controlled by water permeability of asemipermeable membrane and the osmotic properties of therapeutic andosmotic agent in the lumen. Trospium chloride has a high watersolubility and is its own osmotic agent; no additional osmotic agent isincluded. This particular device was designed to deliver trospiumchloride at a rate of approximately 10 mg/day.

The system was placed in deionized water at 37° C., and the rate ofrelease of the trospium was determined. The in vitro results(average±SD, n=3) are shown in FIG. 13. As can be seen, the averagedaily release rate was approximately 10 mg/mL. Thus, it was determinedthat the system can be tailored to provide a desired daily releaseprofile of trospium chloride.

Example 3

Trospium releasing intravesical devices were manufactured for in vitrorelease characterization, according to the parameters of Table 1. Thedevices were manufactured using one of two types of silicone housingparts. One type (RW) included an annular tube having a wall thickness of0.2 mm bounding the drug reservoir lumen and having a 50A durometer. Theother type (TW) included an annular tube having a wall thickness of 0.4mm bounding the drug reservoir lumen and having a 35A durometer. Both ofthe types of silicone parts had a drug reservoir lumen inner diameter of2.64 mm. All of the devices had a 150 μm diameter laser-drilled orifice,which was approximately centered in the sidewall of the silicone part.Systems were assembled using plugs of different lengths. Systems eithercontained two plugs, one on each end, or one plug with a spacer on theother end of the system that seals that end of the reservoir (i.e., suchthat no microchannels can form at that end). The drug reservoir lumen ofeach system was filled with approximately 996 mg of trospium chloridetablets, with a composition of 95 percent trospiumchloride-polyvinylpyrrolidone (PVP) granules with a 97:3 ratio (percentw/w), and 5 percent polyglycol 8000 PF (PEG 8k) by mass. Trospiumchloride acted as both the active agent and osmotic agent to drive theosmotic drug release mechanism. A total of 42 device systems were usedfor this in vitro stability characterization. All systems wereirradiated.

For the RW systems, first-order trospium release kinetics was observedafter initial peak release rates of approximately 18 to 24 mg/day by day7. The TW systems had an initial peak release rate between 10 and 15mg/day with constant release rates of 10 to 14 mg/day over the next 35days. The RW systems displayed a higher cumulative release than the TWsystems, but the number of plugs present in the systems and the lengthof the plugs had no effect on the release rates of the systems.

TABLE 1 Device information Drug Type of Tablet Core Silicone Plug SystemMass Length Body Length Plug Spacer No. (mg)* (cm)** Part (mm) No. No. 1 1000.6 15.6 RW  5 1 1  2  993.5 15.6  3 1003.3 15.5  4  999.8 15.7 20  5  998.3 15.8  6  989.9 15.5  7  990.9 15.6  8 1 1  8  994.5 15.4  9 995.3 15.6 10  993.2 15.5 2 0 11  999.8 15.5 12  992.9 15.5 13  992.715.5 16 1 1 14  991.1 15.4 15  993.9 15.6 16  996.8 15.7 2 0 17  991.315.6 18  986.6 15.7 19 992  15.4 TW  5 1 1 20  994.5 15.3 21 1000.6 15.422  997.6 15.5 2 0 23  990.5 15.3 24 1000.8 15.5 25  990.9 15.4  8 1 126 1001.3 15.4 27  992.1 15.4 28 1000.9 15.6 2 0 29 1002.8 15.6 301002.2 15.7 31  997.8 15.3 16 1 1 32  994.9 15.5 33 1000.7 15.5 34 996.7 15.6 2 0 35  998.9 15.5 36  992.2 15.5 37 — 15   RW  8 2 0 38 —15   39 — 15   40 — 15   TW 41 — 15.1 42 — 15.1 *The total linear lengthof the tablets was approximately 14.9 cm when the tablets were seriallylaid out **Approximate linear length between two spacer surfaces facingthe tablets when the system was straightened

All irradiated units were used for in vitro release testing. Each unitwas placed in a glass jar filled with 300.00+/−0.05 g degassed deionizedwater and put in an environmental chamber kept at 37° C. Samples weretaken from each jar at predetermined time points (T=1, 2, 4, 7, 10, 14,21, 28, 35, and 42 days). At each time point, release jars were inverted15 times and a 1 mL sample was taken and replaced with 1 mL freshrelease media. At days 14 and 28, the release media was fully replaced.Trospium time point samples were analyzed using high-performance liquidchromatography (HPLC) operated by MassLynx.

Trospium chloride release rate (mg/day) at a given time point T(i) wasestimated using a backward difference method according to Equation 1:

$\begin{matrix}{{{Release}\mspace{14mu}{rate}\mspace{14mu}{at}\mspace{14mu}{T(i)}\left( {{mg}\mspace{14mu}{{FBE}/{day}}} \right)} = \frac{{M(i)} - {M\left( {i - 1} \right)}}{{T(i)} - {T\left( {i - 1} \right)}}} & \left( {{Eq}.\mspace{14mu} 1} \right)\end{matrix}$

where M(i) and M(i−1) are cumulative amount released at the current timepoint T(i) and the previous time point T(i−1), respectively. Thecumulative amount of trospium released data seen in FIG. 22 was used tocreate the trospium chloride rate of release profiles seen in FIGS. 18through 21. The initial drug load was used to estimate the percentamount of trospium released which can be seen in FIG. 23. The averagecumulative percent of trospium released for each configuration type canbe seen in Table 2 below.

TABLE 2 Average percent released at days 4, 21, and 42 for each deviceconfiguration System Characteristics Plug/ Plug Average cumulativePercent Released (%) Tubing Spacer Length Media Day 4 Day 21 Day 42 Typeconfiguration (mm) n Type Avg RSD (%) Avg RSD (%) Avg RSD (%) RW 1 plugand  5 3 DI 1.64 33.45 38.76 2.81 57.19 4.88 50A 1 spacer Water 2 plugs 5 2.36  8.28 38.31 2.62 57.33 2.43 1 plug and  8 0.54 124.04  37.423.70 56.62 2.82 1 spacer 2 plug  8 2.41  8.68 38.56 4.83 58.31 4.76 1plug and 16 1.29 34.07 37.29 2.76 56.17 1.44 1 spacer 2 plugs 16 1.2055.14 37.54 1.77 55.75 0.94 TW 1 plug and  5 0.59 38.33 23.77 5.97 45.812.95 35A 1 spacer 2 plugs  5 1.09 15.34 24.28 1.30 46.43 0.77 1 plug and 8 0.58 31.10 24.55 2.03 46.71 2.57 1 spacer 2 plugs  8 0.93 36.62 23.684.07 45.62 1.26 1 plug and 16 0.48 49.24 23.52 5.14 45.24 3.46 1 spacer2 plugs 16 0.58 45.41 22.75 5.11 45.15 2.86 RW 2 plugs  8 4.92 11.9544.77 1.32 68.10 6.76 50A TW 2 plugs  8 2.02 15.43 24.82 0.52 49.24 4.2535A

RW and TW systems with two plugs (see FIG. 18). First-order trospiumrelease kinetics were observed after an initial release rate ofapproximately 18 to 20 mg/day at approximately 7 days since the releaseexperiment started for RW systems with different plug lengths of 5, 8,and 16 mm. After 7 days, a steady decrease in the release rates of theRW systems was observed. At the end of the 42-day experiment, therelease rate averaged 5 to 6 mg/day. The initial release rate for TWsystems was observed to be approximately 12 to 13 mg/day. After thefirst 10 days, the release rates remained approximately constant atabout 11 to 13 mg/day for the first 35 days. After the first 35 days,first-order trospium release kinetics was observed. At the end of the42-day experiment, the release rates averaged 8 to 9 mg/day. No changein release rate occurred with a change in plug length. All RW systemswith plugs length of 5, 8, or 16 mm displayed the same release profiles,and all TW systems with plugs length of 5, 8, or 16 mm displayed thesame release profiles.

System with one plug and one spacer (see FIG. 19). First-order trospiumrelease kinetics were observed after an initial release rate ofapproximately 20 to 23 mg/day at approximately 7 days since the releaseexperiment started for RW systems with different plug lengths of 5, 8,and 16 mm. After 7 days, a steady decrease in the release rates of theRW systems was observed. At the end of the 42-day experiment, therelease rate averaged 5 to 6 mg/day. The initial release rate for TWsystems was observed to be approximately 13 to 15 mg/day. After thefirst 10 days, the release rates remained approximately constant atabout 10 to 13 mg/day for the first 35 days. After the first 35 days,first-order trospium release kinetics was observed. At the end of the42-day experiment, the release rates averaged 8 to 9 mg/day. No changein release rate occurred with a change in plug length. All RW systemswith plugs length of 5, 8, or 16 mm displayed the same release profiles,and all TW systems with plugs length of 5, 8, or 16 mm displayed thesame release profiles.

System with one plug and one spacer as compared to two plug systems (seeFIG. 20). All RW systems with plugs length of 5, 8, or 16 mm displayedthe same release profiles, and all TW systems with plugs length of 5, 8,or 16 mm displayed the same release profiles. Additionally, the RW andTW systems displayed no change in release rate when comparing the oneplug systems versus the two plug 8 mm systems from a lot tested inminipigs. Both a change in plug length and the number of plugs presentdid not change the release rate of the trospium chloride systems.

Systems with 8 mm plugs (see FIG. 21). First-order trospium releasekinetics were observed after an initial release rate of approximately 19to 24 mg/day at approximately 7 days since the release experimentstarted for RW systems with different plug amounts of 8 mm length. After7 days, a steady decrease in the release rates of the RW systems wasobserved. At the end of the 42-day experiment, the release rate averaged5 to 6 mg/day. The initial release rate for TW systems was observed tobe approximately 10 to 13 mg/day. After the first 10 days, the releaserates remained approximately constant at about 10 to 14 mg/day for thefirst 35 days. After the first 35 days, first-order trospium releasekinetics was observed. At the end of the 42-day experiment, the releaserates averaged 8 to 10 mg/day. No change in release rate occurred with achange in the number of plugs each system contained that were 8 mm inlength. All RW systems with plugs length of 8 mm displayed the samerelease profiles when there was one or two plug in the system, and allTW systems with plugs length of 8 mm displayed the same release profileswhen there were one or two plugs in the system.

In conclusion, osmotic trospium releasing devices assembled with 0.2 mmwall thickness (RW) and 0.4 mm wall thickness (TW) loaded withapproximately 917 mg of trospium chloride were built and an in vitrorelease experiment was performed in 37° C. DI water as the releasemedium. For RW systems, first-order trospium release kinetics wereobserved after an initial release rate of approximately 18 to 24 mg/dayat approximately 7 days after the release experiment started. Theinitial release rate for the TW systems was approximately 10 to 15mg/day. For the TW systems, the release rate remained approximatelyconstant at about 10 to 14 mg/day for the first 28 days. After the first35 days, first-order trospium release kinetics were observed. Therefore,RW systems had a high initial peak release rate and higher cumulativerelease of the overall drug load by the end of the experiment. TWsystems had a more constant release rate for the first 35 days and alower cumulative release of the overall drug load. There was no changein the release rate profiles with a change in the number of plugspresent or the length of the plugs. All the RW systems displayedapproximately the same release rate, cumulative release, and percentrelease. All the TW systems displayed approximately the same releaserate, cumulative release, and percent release.

Example 4

Trospium releasing intravesical devices with drug release opening(s)were manufactured for in vitro release testing. Dual lumen siliconetubes were used to construct the systems. The small lumen contained abi-oval shape wireform and the large lumen was filled with trospiummini-tablets having a composition (percent w/w) of 92 percent trospiumchloride, 3 percent PVP, and 5 percent PEG 8K. The amount of trospiumchloride loaded in each system was approximately 910 to 920 mg.

Four punched hole configuration. FIGS. 9A-9B show a configuration wherefour punched holes are present, two punched holes in the sidewall of thehousing near each end of the drug core. The holes were positioned overparylene C coated silicone restraining plugs with a length of 5 mm andouter diameter (OD) of 2.77 mm. Silicone adhesive behind the restrainingplugs was used to fix the restraining plugs in place and the adhesivesealed the ends of the lumen. A bi-oval shaped wireform was insertedinto the small lumen of the tube, and silicone adhesive was applied intothe small lumen to fix the wireform in place and allowed to cure forapproximately 24 hours, after which time the ends were trimmed to 5 mmfrom the end of the restraining plugs. The silicone restraining plugswere oversized; the inner diameter of the silicone tube was 2.64 mmwhile the outer diameter of the silicone restraining plugs was 2.77 mm.The parylene coating on the restraining plug was used to prevent gammairradiation induced adhesion at the silicone-to-silicone interface aftergamma irradiation was used for product sterilization. The punched holeswere placed at 2 to 3 mm from each end of the drug core. The punchedholes over the oversized restraining plugs were designed to serve asdrug release outlets as osmotic pressure inside the drug chamber isbuilt up.

The location and the number of holes can vary depending on how many andwhere the restraining plugs are located along the length of the tube.For example, if only one restraining plug and two punched holes arepresent in the middle of the tube, there will be two drug releaseopenings in the middle of the tube.

Two slit opening configuration. FIGS. 10A-10B show a configuration wheretwo slits are present in the device, one slit in the sidewall of thehousing near each end of the drug core. Parylene C coated siliconerestraining plugs with a length of 5 mm and outer diameter of 2.77 mmwere inserted into the tube and then the slits were created by razorblade. The razor blade passed through the tube wall and penetratedpartially into the restraining plug, so silicone material from the wallwas not removed, in contrast to punched holes where wall material isremoved. Silicone adhesive behind the restraining plugs was used to fixthe restraining plugs in place and the adhesive sealed the ends of thelumen. The slits were placed at 2 to 3 mm from each end of the drugcore. A bi-oval shape wireform was inserted into the small lumen of thetube, and silicone adhesive was applied into the small lumen to fix thewireform in place and allowed to cure for approximately 24 hours afterwhich time the ends were trimmed to 5 mm from the end of the restrainingplugs. The silicone restraining plugs were oversized; the inner diameterof the silicone tube was 2.64 mm while the outer diameter of thesilicone restraining plugs was 2.77 mm. The parylene coating on therestraining plug was used to prevent gamma irradiation induced adhesionat the silicone-to-silicone interface after gamma irradiation was usedfor product sterilization. A small piece of paper was inserted into eachslit to prevent possible adherence and closure of the wall during theirradiation, and then was removed afterward irradiation. The slits overthe oversized restraining plugs were designed to serve as drug releaseoutlets as osmotic pressure inside the drug chamber is built up.

The location and the number of slits can vary depending on how many andwhere restraining plugs are located along the length of the tube. Forexample, if only one restraining plug is present in the middle of thetube, there can be one slit in the middle of the tube.

Three opening system (one laser-drilled orifice and two plugs). FIGS. 2and 3A show a three opening system having a laser-drilled aperture witha 150 micron diameter in the middle of the tube, and two plugs (seeFIGS. 3B and 3C), which had the outer diameter of 2.77 mm and the lengthof 8 mm. The plugs were made of silicone and coated with parylene C, andeach plug included a bevel at one end (see FIGS. 3A-3C). Siliconeadhesive was applied in the region created by the bevel end and thelarge lumen to fix the plugs in place but the adhesive did not seal theends of the lumen. FIGS. 3B and 3C shows one end of the three openingsystem and the plug is shown. FIGS. 1C and 1D show the diagram of suchone-way valve; each plug, oversized in the large lumen, forms one-wayvalve once osmotic pressure in the large lumen is built up.

Unlike the punched holes over oversized restraining plugs (FIGS. 9A-9B)and the slits over oversized restraining plugs (FIGS. 10A-10B) and theplugs (FIGS. 1C, 1D, 3B, 3C), the laser-drilled hole is an aperture witha pre-defined opening, which is present regardless of the presence ofosmotic pressure in the drug reservoir (i.e., the large lumen or drugcompartment lumen).

In vitro release testing. Six types of systems were tested for in vitrorelease, according to the parameters in Table 3. The shapes of all typesof systems were bi-oval. However, the number and configuration of drugrelease openings, silicone tube wall thickness (RW or TW), and siliconetube hardness (50A and 35A) differed depending on system type. All ofthe systems were gamma irradiated (25-40 kGy) before being tested for invitro release.

TABLE 3 List of tested systems in in vitro release Type System Siliconetube 1 Four opening system with Regular wall (RW) four punched holes andRW tube silicone tube with a large (as in FIGS. 9A-9B) lumen with 2.64mm 2 Two opening system with two slits ID and 0.20 mm and RW tube (as inFIGS. wall, and 50 A 10A-10B) durometer 3 Three opening system with alaser-drilled orifice and two plugs and RW tube (as in FIGS. 2-3) 4 Fouropening system with four Thick wall (TW) silicone punched holes and TWtube with a large lumen tube (as in FIGS. 9A-9B) with 2.64 mm ID and 5Two opening system with two slits 0.41 mm wall, and TW tube (as in FIGS.and 35 A durometer 10A-10B) 6 Three opening system with a laser-drilledorifice and two plugs and TW tube (as in FIGS. 2-3)

In vitro release with 0.20 mm wall (RW) tube. The systems were placed in300 grams of deionized water at 37° C., and time point samples werecollected at pre-determined time points to construct in vitro releaseprofiles. FIGS. 14 and 15 show trospium chloride release rates andcumulative amount released over time for Type 1, 2, and 3 in Table 3. Nonoticeable difference was observed in the drug release characteristicsbetween two opening systems (with slits) and four opening systems (withpunched holes), which supports osmotically controlled drug release.However, the three opening system, which has a pre-defined laser-drilledaperture and two plugs, showed higher overall cumulative release amountcompared with two opening systems and four opening systems.

In vitro release with 0.41 mm wall (TW) tube. The systems were placed in300 grams of deionized water at 37° C., and time point samples werecollected at pre-determined time points to construct in vitro releaseprofiles. FIGS. 16 and 17 show trospium chloride release rates andcumulative amount released over time for Type 4, 5, and 6 in Table 3. Nonoticeable difference was observed in the drug release characteristicsbetween two opening systems (with slits) and four opening systems (withpunched holes), which supports osmotically controlled drug release.However, three opening system, which has a pre-defined laser-drilledaperture and two plugs, showed higher overall cumulative release amountcompared with two opening systems and four opening systems.

Example 5

Devices were manufactured to compare a system having two end restrainingplugs and no sidewall orifice (such as disclosed in U.S. PatentApplication Publication 2016/0008271 to Lee) with a system havingpreformed ports in the sidewall adjacent restraining plugs and nosidewall orifice (such as illustrated in FIG. 9). The device parametersare given below in Table 4.

The devices were immersed in deionized water and the release rate of thedrug was measured over time. The results are illustrated in FIG. 24,which demonstrates that the system having the punched holes withadjacent restraining plugs to form the microchannels therebetweenproduces a similar release profile over the 84 day in vitro release testas compared to the prior plug only system. Indeed, the system havingpunched holes with restraining plugs showed a smoother release profileas compared to the plug only system.

TABLE 4 Device parameters for Example 5 Sample Device No. DrugConstituent Constituent IVR Conditions 1 Emerson Tablets, 2.16 mm ID ×100.00 ± 0.05 g of Lot CU06-050, 0.4 mm wall DI water 95% Tros/PVPthickness, Thick for the first 14 days Gran (97:3), Wall, 35 A, plugsand then increased to 5% PEG8K, no orifice 300.00 ± 0.05 g 2.16 mm OD ofDI water for 84 days. Stored at 37° C. 2 2.16 mm ID × 300.00 ± 0.05 g0.4 mm wall of DI water thickness, for 84 days. Stored thick wall, 35 A,at 37° C. 4 punched holes of 0.76 mm diameter each, no orifice

Publications cited herein and the materials for which they are cited arespecifically incorporated by reference. Modifications and variations ofthe methods and devices described herein will be obvious to thoseskilled in the art from the foregoing detailed description. Suchmodifications and variations are intended to come within the scope ofthe appended claims.

What is claimed is:
 1. A method of administering a drug to a patient,comprising: inserting a drug delivery device into a lumen or body cavityof a patient, the drug delivery device comprising: a body that comprisesa wall bounding a reservoir defined within the body, the wall having atleast one preformed through-hole disposed therein and comprising awater-permeable portion, the body comprising an elastic portion, a drugformulation which comprises a drug, the drug formulation being disposedwithin the reservoir, and at least one restraining plug closing off anopening of the body and contacting the elastic portion of the body, theopening being in fluid communication with the reservoir; and permittingin vivo water influx through the water-permeable portion of the wallinto the reservoir to contact the drug formulation to develop ahydrostatic pressure in the reservoir effective to cause the drug toflow from the reservoir through at least one of the preformedthrough-hole, or through one or more microchannels, and out of thedevice and into the lumen or body cavity, wherein the one or moremicrochannels are transiently formed between the elastic portion of thebody and the at least one restraining plug.
 2. The method of claim 1,wherein the body cavity is the bladder of the patient.
 3. A method ofadministering a drug to a patient, comprising: inserting a drug deliverydevice into a lumen or body cavity of a patient, the drug deliverydevice comprising: a tubular body that comprises a wall bounding areservoir defined within the body, the wall comprising a water-permeableportion and an elastic portion having at least one preformed releaseport disposed therein; a drug formulation which comprises a drug, thedrug formulation being disposed within the reservoir; and at least onerestraining plug secured within the reservoir in contact with theelastic portion of the body and adjacent the at least one preformedrelease port; and permitting in vivo water influx through thewater-permeable portion of the wall into the reservoir to contact thedrug formulation to develop a hydrostatic pressure in the reservoireffective to transiently form one or more microchannels between theelastic portion of the body and the at least one restraining plug,extending to the at least one preformed release port, thereby causingthe drug to flow from the reservoir, through the microchannels and theat least one preformed release port, and out of the device and into thelumen or body cavity.
 4. The method of claim 3, wherein the body cavityis the bladder of the patient.
 5. A method of treating a patient in needof treatment for neurogenic detrusor overactivity (NDO) resulting from aspinal cord injury (SCI), the method comprising: locally administeringan effective amount of trospium into the urinary bladder of the patientcontinuously over a treatment period of 30 to 60 days.
 6. The method ofclaim 5, wherein the locally administering an effective amount oftrospium comprises releasing the trospium into urine in the bladder froma drug delivery device located within the patient's bladder.
 7. Themethod of claim 5, wherein the treatment period is 42 days.
 8. Themethod of claim 5, wherein the trospium is released into the bladder ata daily average rate of from about 2 mg/day to about 30 mg/day over thetreatment period.
 9. The method of claim 5, wherein the trospium isreleased into the bladder at a daily average rate of from about 5 mg/dayto about 25 mg/day over the treatment period.
 10. The method of claim 5,wherein the trospium is released into the bladder at a daily averagerate of from about 5 mg/day to about 15 mg/day over the treatmentperiod.
 11. The method of claim 5, wherein the trospium is released intothe bladder at a daily average rate of about 10 mg/day over thetreatment period.
 12. A method of treating a patient in need oftreatment for idiopathic overactive bladder (iOAB) and urinaryincontinence, the method comprising: locally administering an effectiveamount of trospium into the urinary bladder of the patient continuouslyover a treatment period of 30 to 60 days.
 13. The method of claim 12,wherein the locally administering an effective amount of trospiumcomprises releasing the trospium into urine in the bladder from a drugdelivery device located within the patient's bladder.
 14. The method ofclaim 12, wherein the treatment period is 42 days.
 15. The method ofclaim 12, wherein the trospium is released into the bladder at a dailyaverage rate of from about 2 mg/day to about 30 mg/day over thetreatment period.
 16. The method of claim 12, wherein the trospium isreleased into the bladder at a daily average rate of from about 5 mg/dayto about 25 mg/day over the treatment period.
 17. The method of claim12, wherein the trospium is released into the bladder at a daily averagerate of from about 5 mg/day to about 15 mg/day over the treatmentperiod.
 18. The method of claim 12, wherein the trospium is releasedinto the bladder at a daily average rate of about 10 mg/day over thetreatment period.
 19. A drug delivery device comprising: a body thatcomprises a wall bounding a reservoir defined within the body, the wallhaving at least one preformed through-hole disposed therein andcomprising a water-permeable portion, the body comprising an elasticportion; a drug formulation which comprises a drug, the drug formulationbeing disposed within the reservoir; and at least one restraining plugclosing off a respective opening of the body and contacting the elasticportion of the body, the respective opening being in fluid communicationwith the reservoir, wherein the water-permeable portion of the wall isconfigured to permit water to enter the drug delivery device and contactthe drug formulation located in the reservoir, wherein release of thedrug from the device is controlled by (i) release of the drug throughthe at least one preformed through-hole in the wall, and (ii) release ofthe drug through the transient formation of one or more microchannelsbetween the elastic portion of the body and the at least one restrainingplug upon generation within the reservoir of a hydrostatic pressureeffective to form the one or more microchannels.